Capture and elution of bio-analytes via beads that are used to disrupt specimens

ABSTRACT

Lysing may include agitating a specimen in a chamber along with a medium that includes a particulate lysing material that has an affinity for a biological material. Lysing material may include beads or other material which may be coated that facilitates binding. The medium may include a fluid with a high salt or low pH level. The biological material may be eluted by lowering a concentration of salt or increasing a pH level. Lysing materials with two or more different affinities may be employed. Heating may be used. Lysing may be performed in a flow through apparatus.

TECHNICAL FIELD

The present disclosure relates to extraction, capture and elution of biological material, for example nucleic acids such as DNA, from biological specimens using particulate materials. The present disclosure also relates to lysing and in particular to systems, apparatus and methods to perform lysing of a biological material to be lysed using a lysing particulate material.

BACKGROUND

Lysis of biological specimens, for example cell lysis, is used to provide biological materials for compositional analysis. Specific biological materials may include proteins, lipids, and nucleic acids either individually or as complexes. When a cell membrane is lysed, certain organelles—nuclei, mitochondria, lysosomes, chloroplasts, and/or endoplasmic reticulum—may be isolated. Such may be analyzed using methods such as polymerase chain reaction (PCR), electron microscopy, Western blotting or other analysis techniques.

There are numerous approaches to performing lysis. For example, enzymatic approaches may be employed to remove cell walls using appropriate enzymes in preparation for cell disruption or to prepare protoplasts. Another approach employs detergents to chemically disrupt cell membranes. These chemical approaches may adversely affect the resulting product, for example degrading the bio-products being released. Consequently, chemical approaches may, in some instances, not be practical.

Yet another approach employs ultrasound to produce cavitation and impaction for disrupting the cells. Such an approach may not achieve as high a lysis efficiency as may be required or desired for many applications.

Yet still another approach employs beads (e.g., glass or ceramic) which are agitated, for example, via a vortex mixer. Such an approach successfully addresses the issues raised by chemical lysis approaches, yet improvements in such an approach are desirable.

Particular biological materials that are isolated from the interior of cells or viruses for use in a variety of analysis or testing procedures include nucleic acids. These may be isolated and used, for example, in testing for bacterial or viral infections. Nucleic acid analysis or testing for such purposes may provide improved sensitivity or may shorten the time between incidence of an infection and appearance of a positive test, compared to results obtained from more traditional antibody testing. Nucleic acid analysis or testing typically involves extraction and isolation of a nucleic acid of interest, e.g., deoxyribonucleic acid (DNA), from the biological specimens, followed by amplification reactions, such as PCR. Amplification of the isolated nucleic acid increases the sensitivity of detection and identification of the resulting nucleic acid.

Commonly used techniques for rapid extraction and isolation of nucleic acids, in particular DNA, from cells utilize membranes or magnetic beads made from silica or from other materials that capture DNA nonspecifically on the basis of the polyanionic chemistry of DNA. Most such techniques rely on the use of harsh reagents, such as chaotropic salts, e.g., guanadinium hydrochloride, or proteases, to lyse cells to free the DNA. The harsh reagents used in such methods of DNA isolation are not compatible with subsequent amplification reactions. The reagents must thus be thoroughly removed, often by numerous wash steps, prior to elution and subsequent use or analysis of the isolated DNA. An approach that eliminates such manipulations, particularly the use of harsh reagents, could advantageously improve the efficiency of the process and the utility of the isolated product, and could thus simplify and optimize processing of cell-contained DNA for such purposes.

BRIEF SUMMARY

There is a need for particle-based systems and methods that efficiently obtain biological material. Such improved systems and methods may reduce the amount of time required to process a sample (i.e., a sample from which to obtain the biological material) and/or to increase throughput. Such may also increase the degree of thoroughness of obtaining the material, yielding greater amounts of material from a given sample size. There is also a need for systems and methods for lysis, capture and elution of biological material without separate processing of particles on which the biological material is captured. In particular, there is a need for such systems and methods that allow lysis, capture and elution of biological materials within the same system by simply controlling chemical composition and flow of reagents within the system. There is also a need for systems and methods to lyse cells without use of harsh reagents. Such may avoid wash steps during processing of biological material captured by particle-based systems. There is also a need for systems and methods that may allow sample heating integrated within a system. There is also a need for systems and method for specific capture of cell components. There is also a need for lysing equipment that is small and hence portable, and that is relatively inexpensive yet sufficiently robust to withstand travel or harsh operating environments.

A method of obtaining biological material may be summarized as including introducing a specimen containing the biological material into a chamber and agitating the specimen in the chamber along with a medium that includes a particulate lysing material and a fluid, to mechanically lyse the specimen, the particulate lysing material having an affinity for the biological material in the presence of the fluid, the affinity being sufficient to bind at least some of the biological material to at least some of the particulate lysing material. The particulate lysing material may include a plurality of beads and agitating the specimen in the chamber along with a medium that includes a particulate lysing material and a fluid to lyse the specimen may include agitating the specimen in the chamber along with the plurality of beads. The particulate lysing material may include at least one of a plurality of ceramic beads, a plurality of glass beads, a plurality of zirconium beads, a plurality of silica beads, a plurality of sand, or a plurality of beads with a metal core coated by a material such as latex that can be modified to have an affinity for or to bind to a biomaterial. Agitating the specimen in the chamber along with a medium that includes a particulate lysing material and a fluid to lyse the specimen may include agitating the specimen in the chamber along with the at least one of the plurality of ceramic beads, the plurality of glass beads, the plurality of zirconium beads, the plurality of silica beads, or the plurality of sand. Agitating the specimen in the chamber along with a medium that includes a particulate lysing material and a fluid to lyse the specimen may include agitating the specimen in the chamber along with particulate lysing material having diameters or smallest lateral dimensions in the range of approximately 10 microns to approximately 600 microns.

The fluid may have a high salt concentration and agitating the specimen in the chamber along with a medium that includes a particulate lysing material and a fluid to lyse the specimen may include agitating the specimen in the chamber with the fluid having the high salt concentration. A fluid having a high salt concentration may include a fluid having a salt concentration of at least about 500 millimolar.

The fluid may have a low pH and agitating the specimen in the chamber along with a medium that includes a particulate lysing material and a fluid to lyse the specimen may include agitating the specimen in the chamber with the fluid having the low pH. A fluid having a low pH may include a fluid having a pH no lower than about 4.

The medium that includes a particulate lysing material and a fluid in the chamber may be free of any chemical lysing agents.

Agitating the specimen in the chamber along with a medium that includes a particulate lysing material and a fluid to lyse the specimen may include oscillating an arm on which the chamber is mounted. Agitating the specimen in the chamber along with a medium that includes a particulate lysing material and a fluid to lyse the specimen may include driving an impeller having a number of blades located at least partially in the chamber.

The method may further include eluting the biological material from at least the particulate lysing material. Eluting the biological material from at least the particulate lysing material includes at least one of lowering a salt concentration or increasing a pH of an environment in which the particulate lysing material is contained. Lowering a salt concentration or increasing a pH of an environment in which the particulate lysing material is contained may include lowering a salt concentration or increasing a pH of the fluid in the chamber.

Eluting the biological material from at least the particulate lysing material may include eluting the material without any washing. Eluting the biological material from at least the particulate lysing material may include eluting at least one of a DNA material, a protein or polypeptide material, or another cell component material.

The method may further include heating the biological material after lysing the specimen.

The method may further include slowing the specimen through the chamber in a first direction at a first time and at a first rate, and in a second direction, opposite the first direction, at a second time and at a second rate. The method may include a medium having a particulate lysing material that may include two different particulate lysing materials each having been modified to bind biological materials having different chemistries, a first particulate lysing material having been modified to bind a biological material having a first chemistry and a second particulate lysing material having been modified to bind a biological material having a second chemistry. The biological material having a first chemistry may be DNA, and the biological material having a second chemistry may be a protein or polypeptide. The method for binding protein or polypeptide may further include labeling the protein or polypeptide with a solution phase tagged ligand during capture to facilitate subsequent detection of the protein or polypeptide. The method may further comprise separately eluting biological material of a first chemistry and biological material of a second chemistry from the solid phase. The separately eluted biological materials may be DNA and protein or polypeptide. DNA may be eluted with low pH and protein or polypeptide may be separately eluted with urea.

The method may further include separately transferring unbound biological material for further processing. The unbound biological material may be transferred to a separate chamber or container.

The method may include capturing the biological material by a particulate material having bound thereto via a photocleavable linkage a receptor specific for the biological material and eluting a complex of the biological material and the receptor by exposure to light of a wavelength suitable to cleave the photocleavable linkage. The receptor bound to the particulate material may be, for example, a sequence specific capture probe suitable to specifically bind a DNA or an antibody suitable to specifically bind a protein or polypeptide.

A system to lyse specimens and isolate specific biological materials from the lysed specimens may be summarized as including a chamber to receive a specimen containing the biological material to be isolated therefrom; a medium that includes a particulate lysing material and a fluid, the particulate lysing material having an affinity for the biological material in the presence of the fluid, the affinity sufficient to bind at least some of the biological material to at least some of the particulate lysing material; and an agitator selectively operable to agitate the specimen in the chamber along with the medium that includes the particulate lysing material and the fluid to mechanically lyse the specimen and concurrently bind at least some of the biological material to at least some of the particulate lysing material. The particulate lysing material may include a plurality of beads. The particulate lysing material may include at least one of a plurality of ceramic beads, a plurality of glass beads, a plurality of zirconium beads, a plurality of silica beads, or a plurality of sand. The particulate lysing material may have a diameter or smallest lateral dimension in the range of approximately 10 microns to approximately 600 microns.

The fluid may have a high salt concentration. The salt concentration may be at least about 200 millimolar. The fluid may have a low pH. The pH may be no lower than about 4.

The medium in the chamber may be free of any chemical lysing agents.

The agitator may include at least one motor and an arm that holds the chamber, the arm coupled to the motor to be oscillatingly driven thereby. The agitator may include at least one motor and an impeller that is positionable at least partially in the chamber, the impeller coupled to the motor to be oscillatingly driven thereby.

The biological material to be isolated by the system may include at least one of a DNA material, a protein or polypeptide material, or another cell component material.

The system may further include a pump operable to flow a volume of the specimen through the chamber that exceeds the volume of the chamber. The system may further include a pump operable to flow the specimen through the chamber in a first direction at a first time and at a first rate, and in a second direction, opposite the first direction, at a second time and at a second rate.

The system may further include a heater in thermal contact with a pump, the heater selectively operable to heat the biological material.

The system may include particulate lysing material that has been modified to bind biological materials of two different chemistries, a first particulate lysing material that has been modified to bind biological material having a first chemistry and a second particulate lysing material that has been modified to bind biological material having a second chemistry. The biological material having a first chemistry may be DNA, and the biological material having a second chemistry may be protein or polypeptide.

The system may further include a chamber to separately received unbound biological material.

BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWINGS

In the drawings, identical reference numbers identify similar elements or acts. The sizes and relative positions of elements in the drawings are not necessarily drawn to scale. For example, the shapes of various elements and angles are not drawn to scale, and some of these elements are arbitrarily enlarged and positioned to improve drawing legibility. Further, the particular shapes of the elements as drawn are not intended to convey any information regarding the actual shape of the particular elements, and have been solely selected for ease of recognition in the drawings.

FIG. 1A is a front elevational view of an apparatus to perform material lysis, according to one illustrated embodiment.

FIG. 1B is a front, right side, top isometric view of the apparatus of FIG. 1A.

FIG. 1C is a front, left side, bottom isometric view of the apparatus of FIG. 1A.

FIG. 2A is a front elevational view of the apparatus of FIG. 1A with a front cover removed, according to one illustrated embodiment.

FIG. 2B is a front, right side, top isometric view of the apparatus of FIG. 2A.

FIG. 2C is a front, right side, bottom isometric view of the apparatus of FIG. 2A.

FIG. 3 is a front, right side isometric view of a motor and drive mechanism of the apparatus of FIGS. 1A-2C.

FIG. 4 is a schematic view of a system to perform flow-through processing, including an apparatus to perform material lysis, an upstream subsystem to provide material to be lysed, a downstream subsystem to analyze material that has been lysed, and a control subsystem, according to one illustrated embodiment.

FIG. 5 is a cross-sectional view of a container having a chamber that houses material to be lysed, particulate lysing material, and material that has been lysed, according to one illustrated embodiment particularly useful in flow-through lysing.

FIG. 6 is a flow diagram of a method of operating an apparatus, such as the apparatus of FIGS. 1A-4, to perform lysing.

FIG. 7 is a flow diagram of a method of pumping material to be lysed in a flow-through lysing system such as that of FIG. 4 according to one embodiment.

FIG. 8 is a flow diagram of a method of pumping material to be lysed in a flow-through lysing system such as that of FIG. 4, according to another illustrated embodiment.

FIG. 9 is a flow diagram of a method of pumping material to be lysed in a flow through lysing system such as that of FIG. 4, according to yet another illustrated embodiment.

FIG. 10 is a flow diagram of a method of pumping material to be lysed in a flow-through lysing system such as that of FIG. 4, according to still another illustrated embodiment.

FIG. 11 is a flow diagram of a method of evacuating lysed material in a flow-through lysing system such as that of FIG. 4, according to one illustrated embodiment.

FIG. 12 is a flow diagram of a method of evacuating lysed material in a flow-through lysing system such as that of FIG. 4, according to another illustrated embodiment.

FIG. 13 is a method of pumping material to be lysed in a flow-through lysing system such as that of FIG. 4, according to a further illustrated embodiment.

FIG. 14 is a flow diagram of a method of pumping material to be lysed in a flow-through lysing system such as that of FIG. 4, according to still a further illustrated embodiment.

FIG. 15 is a method of operating a flow-through lysing system such as that of FIG. 4 to analyze lysed material, according to one illustrated embodiment.

FIG. 16 is an exploded isometric view of a lysing apparatus according to another illustrated embodiment.

FIG. 17 is a schematic diagram of a lysing system including a lysing apparatus, an upstream subsystem to provide material to be lysed, a downstream subsystem to analyze material that has been lysed, and a control subsystem, according to another illustrated embodiment.

FIG. 18 is a front elevation view of a lysing apparatus and pipette according to one illustrated embodiment.

FIG. 19 shows a flow diagram of a method of operating a lysing apparatus such as that of FIGS. 16 and 17, according to one illustrated embodiment.

FIG. 20 is a flow diagram of a method of evacuating material that has been lysed from a chamber in operating a lysing apparatus such as that of FIGS. 16 and 17, according to another illustrated embodiment.

FIG. 21 is a flow diagram of a method of receiving material to be lysed in a chamber in operating a lysing apparatus such as that of FIGS. 16 and 17, according to one illustrated embodiment.

FIG. 22 is a flow diagram of a method of pumping material to be lysed into a chamber in operating a lysing apparatus such as that of FIGS. 16 and 17, according to one illustrated embodiment.

FIG. 23 is a flow diagram of a method of pumping material to be lysed into a chamber in operating a lysing apparatus such as that of FIGS. 16 and 17, according to another illustrated embodiment.

FIG. 24 is a flow diagram of a method of operating an impeller of a lysing system such as that of FIG. 16, 17 or 18, according to one illustrated embodiment.

FIG. 25 is a flow diagram of a method of operating an impeller of a lysing system such as that of FIG. 16, 17 or 18, according to one illustrated embodiment.

FIG. 26 is a flow diagram of a method of replacing a micromotor of a lysing system such as that of FIG. 16, 17 or 18, according to one illustrated embodiment.

FIG. 27 is a flow diagram of a method of operating a lysing apparatus such as that of FIG. 18, according to one illustrated embodiment.

FIG. 28 is a flow diagram of a method of operating a lysing apparatus such as that of FIG. 18, according to one illustrated embodiment.

FIG. 29 is a flow diagram of a method withdrawing lysed material from a chamber of a lysing apparatus such as that of FIG. 18, according to one illustrated embodiment.

FIG. 30 is a flow diagram of a method of reusing a micromotor of a lysing apparatus such as that of FIG. 18, according to another illustrated embodiment.

FIG. 31 is a graph showing data representing an efficiency of lysis as a function of lysing duration using an apparatus similar to that of FIG. 4.

FIG. 32 is a graph showing a dependency of lysis efficiency on frequency of oscillation.

FIG. 33 is a graph showing spore lysis as a function of lysis duration for an apparatus similar to that of the embodiment of FIG. 16.

FIG. 34A is a schematic diagram of a bidirectional flow system for lysing, capture and elution including a sample and elution module, a lysing module, a syringe pump, and a heater, according to one illustrated embodiment.

FIG. 34B is a schematic diagram showing valve positions in the sample and elution module during operation of the system in the embodiment of FIG. 34A.

FIG. 35A is a plan view of a lysing apparatus having Luer-Lock couplers, according to one illustrated embodiment, and two syringes coupleable to the lysing apparatus via the couplers.

FIG. 35B is an isometric view of the lysing apparatus of FIG. 51A.

FIG. 36 is a plan view of a plurality of lysing apparatus coupled sequentially to one another, according to one illustrated embodiment.

FIG. 37A is an isometric view of a manifold or array of lysing apparatus, according to one illustrated embodiment.

FIG. 37B is an isometric view of the manifold or array of lysing apparatus carried by a frame, according to one illustrated embodiment, the lysing apparatus positioned to deposit lysed material into respective wells of a plate.

FIG. 38A is a side elevational view of a stopcock style lysing device, according to one illustrated embodiment, showing an inner portion rotated or configured to provide a first flow path via two selected ports.

FIG. 38B is a side elevational view of the stopcock style lysing device of FIG. 38A, showing the inner portion rotated or configured to provide a second flow path via two selected ports.

FIG. 39A is an exploded isometric view of a stopcock style lysing device, according to one illustrated embodiment, showing an inner vessel having an open bottom portion, the inner vessel in a first orientation with respect to an outer vessel.

FIG. 39B is an isometric view of a stopcock style lysing device of FIG. 39A, showing an inner vessel received in an outer vessel, and an drive device including a motor and impeller received in the inner vessel.

FIG. 39C is an isometric view of the inner vessel of FIG. 39A, showing the inner vessel in a second orientation, different from the orientation illustrated in FIG. 39A.

FIG. 40A is an exploded side elevational view of a stopcock style lysing device, according to another illustrated embodiment, showing an inner vessel with a closed bottom portion.

FIG. 40B is an bottom plan view of a stopcock style lysing device of FIG. 40A.

DETAILED DESCRIPTION

In the following description, certain specific details are set forth in order to provide a thorough understanding of various disclosed embodiments. However, one skilled in the relevant art will recognize that embodiments may be practiced without one or more of these specific details, or with other methods, components, materials, etc. In other instances, well-known structures associated with micromotors, controllers including motor controllers, and control systems such as programmed general purpose computing systems and the like have not been shown or described in detail to avoid unnecessarily obscuring descriptions of the embodiments. In other instances, methods commonly known for use with and manipulation of nucleic acids, proteins, polypeptides, and other biological materials have not been described as they would be readily available to those of ordinary skill in the art of such materials. Such common methods include, for example, PCR and heat denaturation of DNA.

Unless the context requires otherwise, throughout the specification and claims which follow, the word “comprise” and variations thereof, such as, “comprises” and “comprising” are to be construed in an open, inclusive sense, that is, as “including, but not limited to.”

Reference throughout this specification to “one embodiment” or “an embodiment” means that a particular feature, structure or characteristic described in connection with the embodiment is included in at least one embodiment. Thus, the appearances of the phrases “in one embodiment” or “in an embodiment” in various places throughout this specification are not necessarily all referring to the same embodiment. Furthermore, the particular features, structures, or characteristics may be combined in any suitable manner in one or more embodiments.

As used in this specification and the appended claims, the singular forms “a,” “an,” and “the” include plural referents unless the content clearly dictates otherwise. It should also be noted that the term “or” is generally employed in its sense including “and/or” unless the content clearly dictates otherwise.

The headings and Abstract of the Disclosure provided herein are for convenience only and do not interpret the scope or meaning of the embodiments.

A number of embodiments of lysis apparatus, systems and methods of use are described herein. The lysis apparatus and systems perform lysis on a material to be lysed using lysing particulate material, to produce lysed material or material that has been lysed. The material to be lysed may take the form of biological materials, for example cells, spores, tissue, yeast, fungi, plants, bacteria, etc., typically suspended in a liquid medium. The lysing particulate material may take a variety of forms. While often referred to herein as beads, the term bead is not meant to be limiting with respect to size or shape. The beads may, for example, take the form of ceramic beads, glass beads, zirconium beads, zirconium/silica beads, metal beads, plastic beads, sand, and/or particles of any such materials other than beads. The lysed material may likewise take a variety of forms, for example nucleic acids, polypeptides, proteins, organelles-nuclei, mitochondria, lysosomes, chloroplasts, endoplasmic reticulum, etc.

Various embodiments of the material separation and/or lysis apparatus and systems may, for example, operate in: 1) a batch mode, 2) flow-through stop or semi-batch mode, or 3) continuous flow-through mode. In batch mode, a container having a chamber holding a sample of material to be lysed is located in a holder and oscillated. The container is removed after sufficient oscillation and the lysed material is recovered. In the flow-through stop or semi-batch mode, a sample of material to be lysed flows into to fill the chamber. The container is then oscillated until sufficiently lysed. The chamber is evacuated of the lysed material. In the flow-through mode, a sample of material to be lysed flows through the chamber of the container during oscillation at a desired flow rate, providing a desired or defined residence time within the chamber. In the flow-through stop or semi-batch mode, the sample may be abutted by an immiscible liquid or gas and the chamber may be evacuated by a blast of a fluid, for example a liquid or a gas.

At least some of the embodiments take advantage of the understanding that the forces responsible for mechanical rupture of biological samples scale with the oscillation frequency squared, and that by employing relatively small sample sizes, the various embodiments described herein can achieve relatively higher frequencies than commercially available apparatus, resulting in rapid and efficient lysis.

A number of embodiments of systems and methods for extraction, capture and elution of biological materials, in particular nucleic acids such as DNA, are described herein. Biological specimens, such as cells or viruses, may be lysed by mechanical disruption in a lysing chamber containing particulate material, for example beads made from silica and/or zirconium. The volume of the lysing chamber may be crowded with the particulate material. The particulate material in the lysing chamber may be driven rapidly by an impeller connected to a small motor to lyse the biological specimens. The motor may be disposable. Alternatively, the lysing chamber may be oscillated to drive the particulate material to lyse the biological specimens. Further, treatment of the contents of the lysing chamber may include ultrasonic treatment. Such different types of mechanical disruption allow lysis to occur without the use of harsh chemicals, such as chaotropic agents. In comparison to standard procedures for preparation of biological materials, the procedures disclosed herein may save time by eliminating wash steps that are typically included to remove harsh chemicals. Chemical conditions within the lysing chamber may be controlled during lysis to allow simultaneously lysis of the biological specimen and binding or collection of the biological material released by lysis, e.g., DNA or protein or both, on the particulate material. The apparatus or system may then be operated to alter chemical and/or flow conditions within the lysing chamber to elute the biological material of interest from the particulate material. The systems and methods disclosed herein thus advantageously allow simple, efficient approaches to lysis, capture and elution of biological materials from biological specimens. The surprisingly advantageous approaches involve appropriately timed, simple control of flow direction and chemical compositions of fluids within a lysing system. The biological material, e.g., DNA, may then be subjected to testing or analysis or used for other purposes. The absence of harsh reagents during lysis may not only save time but also yield materials that are more suitable for use in subsequent procedures. Thus, the disclosed systems and methods provide rapid and efficient lysis of specimens, e.g., cells, and capture of biological materials, e.g., DNA, in a single chamber by sequential use of fluids having chemical compositions particularly appropriate for lysis, capture and elution. Various specific embodiments will now be discussed.

FIGS. 1A-1C and 2A-2C show an apparatus 10 operable to perform lysing on a material to be lysed contained in a container 12, according to one illustrated embodiment. In some embodiments, off-the-shelf vials and tubes may be employed as the container 12 to hold specimens of material to be lysed and the lysing particulate material or other material, for example PCR or Eppendorf tubes. While illustrated in FIGS. 1A-1C and 2A-2C in a batch mode, the lysis apparatus 10 may be used in a flow-through stop or semi-batch mode or in a continuous mode as illustrated in FIG. 4.

The container 12 may be removably coupled to an arm 14 via a holder 16. The holder 16 may take a variety of forms. For example, the holder 16 may take the form of a U-shaped clamp or other member. The holder 16 may include a fastener (e.g., screw, bolt, etc.) 16 a operable to secure the holder 16 in a container securing configuration. Alternatively, the holder 16 may be resilient and biased into the container securing configuration.

The arm 14 may be coupled to pivot about an axle 18 such that the container 12 oscillates along an arcuate path 20. Oscillation along an arcuate path 20 achieves confined periodic flow fields with angular accelerations that provide strong particulate flow fields and large shear rates between beads in a liquid solution or slurry. Experiments by the applicants have demonstrated that miniaturized geometries can provide superior lysis through the application of high frequencies (e.g., greater than approximately 100 Hz). Since the relative forces on non-neutral density beads in a liquid scale according to ω²r, where ω represents angular velocity and r is the distance of a bead from the center of rotation, a small increase in angular speed can allow for a substantial decrease in size to attain similar performance. Linear oscillatory motions, even at high frequencies result in little lysis of biological samples, while those with an arc motion may achieve lysis that is superior to commercially available bead-based lysis apparatus. High-speed movies clearly show that linear motions result in periodic concentration of beads followed by expansion of beads away from one another, but relatively little relative motion of beads that is not along the axis of motion. In contrast, where a container oscillates in an arc, the beads are seen to compress to higher density just as a strong swirl is induced, resulting in very effective lysing. Collisions and shearing provided by the relative motion of the suspended beads contribute to the high efficiency of the lysing.

The arm 14 may be a rigid arm, i.e., an arm that does not appreciably bend during oscillation with a load having a mass at least roughly equivalent to an expected load of a container containing a material to be lysed and a lysing particulate material. Alternatively, the arm 14 may be a flexible arm, i.e., an arm that does appreciably bend during oscillation with a load having a mass at least roughly equivalent to an expected load of a container containing a material to be lysed and optionally a lysing particulate material.

As best illustrated in FIGS. 2A-2C and 3 in which a cover plate 24 is removed, the arm 14 may be driven via a motor 22 and a drive mechanism 26, which may take the form of a four-bar linkage. In particular, a shaft 28 of the motor 22 drives a first member such as a bar, here in the form of eccentric cam 30. The eccentric cam 30 is received in a bore 32 of a second member or connecting arm 34. The connecting arm 34 is drivingly coupled to the holder 16 by the axle 18 of a rocker arm 36. The drive mechanism 26 provides a low cost, reliable mechanism to realize relatively high frequency oscillatory motion along the arcuate path 20. While such frequencies may not be considered high for other types of devices, of instance rotating devices or ultra-sonic devices, such frequencies are considered high oscillating type devices.

FIG. 4 shows a flow-through lysis system 400 according to one illustrated embodiment. As described in more detail herein, the flow-through lysis system 400 may be operated in a flow-through stop or semi-batch mode, or in a continuous flow mode.

The flow-through system 400 includes a lysing apparatus 410 and a container 412, which may be similar to those described in previous embodiments. For example, the lysing apparatus 410 may include an arm 414 and holder 416 to hold the container 412 as the container pivotally oscillates about an axle 418.

The flow-through lysis system 400 may include an upstream subsystem 438 to deliver material to be lysed. For example, the upstream subsystem 438 may include a pump 440 operable to pump or otherwise deliver material to be lysed to the container 412. The upstream subsystem 438 may also include a reservoir 442 that holds the material to be lysed.

The upstream subsystem 438 may additionally or alternatively include a mechanism to collect material to be lysed, for example a sampling apparatus 439. The sampling apparatus 439 may be manually operated or may be automatic. The sampling apparatus 439 may, for example, sample the ambient environment, for example the air or atmosphere, water or fluids, soil or other solids. The sampling apparatus 439 may include a vacuum or mechanism to create a negative pressure to extract a sample. The sampling apparatus 439 may include an actuator, for example an arm with a shovel or broom to retrieve samples. The sampling apparatus may include an actuator, for example a needle and syringe to example samples.

The material to be lysed may be delivered via one or more conduits, for example, a tube 444 a to an entrance 446 a of the container 412. The tube 444 a may be reinforced at one or both ends, for example, being reinforced with multiple layers of concentrically arranged tubes 448 a. The tube 444 a may have a length L₁ that is sufficiently long to allow the container 412 and arm 414 to oscillate, while being sufficiently short as to prevent resonance in the tube. The length L₁ would be a function of the density, the rigidity, or the attachment method of the tube 444 a as well as the density, mass and/or rigidity of any material to be lysed carried therein.

The flow-through lysis system 400 may further include a downstream analysis subsystem 449. The downstream analysis subsystem 449 may include one or more downstream analysis apparatus 450. The downstream analysis apparatus 450 may take any of a variety of forms. For example, the downstream analysis apparatus 450 may include a nucleic acid amplification instrument, electron-microscope, western blotting apparatus, mass spectrometer, gas chromatograph, etc.

The downstream analysis subsystem 449 may further include one or more computing systems 452 communicatively coupled to the downstream analysis apparatus 450. The computing system 452 may be coupled to one or more networks 453, for example a local area network (LAN), a wide area network (WAN) such as the Internet, and/or a wireless wide area network (WWAN). The computer system 452 may provide information about the results of an analysis performed on lysed material via the network 453. For example, the computing system 452 may automatically provide an alert or other message to suitable system based on the results of the analysis. Such may, for example, be used to provide an alert when a toxic or dangerous substance or condition is detected.

The downstream analysis apparatus 450 may be fluidly communicatively coupled to an exit 446 b of the container 412 via one or more conduits, for example, tube 444 b. The tube 444 b may be reinforced at one or both ends, for example, by one or more concentrically arranged lengths of tube 448 b. The tube 444 b may have a length L₂ that is sufficiently long as to allow the container 412 and arm 414 to oscillate freely while being sufficiently short as to prevent resonance of the tube 444 b. The length L₂ may be based on the density, the rigidity, or the attachment method of the tube 444 b as well as a density, mass and/or rigidity of any material carried therein.

The flow-through lysis system 400 may further include one or more control systems 454. The control system 454 may take the form of one or more motor controllers and/or computing systems. The control system 454 may be configured to operate the flow-through system 400 in a flow-through stop or semi-batch mode and/or in a flow-through continuous flow mode. The control systems 454 may, for example, be communicatively coupled to control the lysing apparatus 410 and/or pump 440.

The flow-through system 400 provides a number of advantages over batch based apparatus. For example, some types of beads may have an affinity for certain bio-products that are released on lysis, so some of the cell contents may be “lost” due to adsorption on the bead surfaces. The flow-through design may advantageously automatically elute the adsorbed biomolecules. It also avoids difficult or additional acts that may be required in batch mode configurations to evacuate the chamber. For example, the flow-through embodiments may eliminate any possible need to blast the chamber with a fluid such as air to clear the chamber of the lysed material.

FIG. 5 shows a container 512 according to one illustrated embodiment.

The container 512 may have an entrance 546 a to provide fluid communication from an exterior 560 of the container to a chamber 562 of the container 512. The container 512 may include an exit 546 b providing fluid communication between the exterior 560 and the chamber 562 of the container 512. A first tube 544 a may be coupled to the container 512 to provide material to be lysed 564 to the chamber 562 via the entrance 546 a. As noted previously, the tube 544 a may be reinforced, for example, with one or more layers of concentrically arranged tubing 548 a. A second tube 544 b may be coupled to the container 512 via the exit 546 b to remove lysed material 566 via the exit 546 b. In some embodiments, the container 512 may include attachment structures to attach or otherwise couple or secure the tubes 544 a, 544 b. For example, the container 512 may include a ribbed nipple 568 a at the entrance 546 a and/or a ribbed nipple 568 b at or proximate the exit 546 b.

The container includes lysing material 570. The lysing material 570 may take a variety of forms, for example, a plurality of beads. The beads may take a variety of forms including one or more of ceramic beads, glass beads, zirconium beads, zirconium/silica beads, metal beads, plastic beads, sand, and/or metal beads that are coated with a bio-affinity material or receptor, such as a sequence specific probe or an antibody. The beads may have a variety of diameters, for example, between approximately 10 microns and approximately 600 microns.

In the flow through embodiments, the container 512 may include a first filter 572 a positioned relatively proximate the entrance 546 a and a second filter 572 b positioned relatively proximate the exit 546 b. The first and second filters 572 a, 572 b form a particulate retainment area 574 in which the lysing particulate material 570 is retained. In particular, the filters 572 a, 572 b may have a plurality of openings sized to substantially pass the material to be lysed 564 and the lysed material 566, respectively, while blocking the particulate lysing material 570. The container 512 may include one or more structures, for example, tabs or annular ridges 576 a, 576 b to retain the first and second filters 572 a, 572 b in place. Filters may, for example take the form of nylon or stainless steel mesh filter.

The embodiments of FIGS. 1A-5 may advantageously allow extremely high packing densities. In these embodiments, the volume of particulate material may advantageously exceed the volume of material to be lysed or may exceed the volume of material that has been lysed. Additionally or alternatively, these embodiments may advantageously have essentially no air in the chamber. As used herein, essentially no air means that the chamber is free of air other than small bubbles which may be unintentionally entrapped in the chamber. Such may increase lysing efficiency and prevent undesirable heating of the system from friction associated with liquid-air contact line motions.

FIG. 6 shows a method 600 of operating an apparatus such as that illustrated in FIGS. 1A-4 to lyse material, according to one illustrated embodiment.

At 602, material to be lysed is received in the chamber of the container. The chamber may already hold lysing particulate material. At 604, the container is oscillated along an arcuate path. The oscillation produces large variations in movement between respective ones of the lysing particulate material. Such variations are more pronounced than in translational or rotational movements. At 606, the lysed material is removed from the chamber of the container.

FIG. 7 shows a method 700 of pumping material to be lysed in a flow-through lysing system such as the one of FIG. 4, according to one illustrated embodiment.

At 702, the material to be lysed is pumped into the chamber of the container.

FIG. 8 shows a method 800 of pumping material to be lysed in a flow-through lysing system such as that of FIG. 4, according to one illustrated embodiment.

At 802, the material to be lysed is intermittently pumped into the chamber of the container while the container is oscillated. Such is suitable for the flow-through stop or semi-batch mode.

FIG. 9 shows a method 900 of pumping material to be lysed in a flow-through lysing system such as that of FIG. 4, according to another illustrated embodiment.

At 902, the material to be lysed is intermittently pumped into the chamber such that the material to be lysed spends a sufficient time in the chamber to achieve a desired level of lysing. Thus, if it is determined that 30 seconds of oscillation achieves a desired level of lysing, the pump may be intermittently operated to load the chamber with material to be lysed approximately every 30 seconds. Oscillation times of few seconds or tenths of seconds may be suitable. Such operation is suitable for the flow-through stop or semi-batch mode.

FIG. 10 shows a method 1000 of pumping material to be lysed in a flow-through lysing system such as that of FIG. 4, according to another illustrated embodiment.

At 1002, the material to be lysed is intermittently pumped into the chamber such that the chamber is completely evacuated of the lysed material during each cycle of the intermittent pumping. Such is suitable for the flow-through stop or semi-batch mode.

FIG. 11 shows a method 1100 of evacuating lysed material in a flow-through lysing system such as that of FIG. 4, according to another illustrated embodiment.

At 1102, the chamber is evacuated of the lysed material during each cycle of the intermittent pumping by pumping into the chamber more material to be lysed. Such is suitable for the flow-through stop or semi-batch mode.

FIG. 12 shows a method 1200 of operating a lysing apparatus such as that of FIG. 4, according to another illustrated embodiment.

At 1202, the chamber is evacuated of the lysed material each cycle of the intermittent pumping by pumping an inert fluid into the chamber. The inert fluid may take the form of a liquid or gas, and may be immiscible with the lysed material or material to be lysed. Such is suitable for the flow-through stop or semi-batch mode.

FIG. 13 shows a method 1300 of operating a continuous lysing apparatus, according to one illustrated embodiment.

At 1302, the material to be lysed is continuously pumped into the chamber of the container while the container is oscillated. Such is suitable for the flow-through continuous mode.

FIG. 14 shows a method 1400 of operating a flow-through lysing apparatus, according to another illustrated embodiment.

At 1402, a flow rate of the pumping of the material to be lysed is adjusted based at least in part on the length and free volume of the chamber such that the material to be lysed spends sufficient time in the chamber (i.e., desired or defined residence time) to achieve a desired level of lysing. Such is suitable for the flow-through continuous mode.

FIG. 15 shows a method 1500 of operating a flow-through lysing apparatus, such as that of FIG. 4, according to another illustrated embodiment.

At 1502, the lysed material removed from the chamber of the container is directed to at least one analysis device. At 1504, the lysed material is analyzed. Analysis may take a variety of forms, for example analysis with electron-microscope, western blotting, mass spectrometry, gas chromatography, etc. Such is suitable for any of the modes, and particularly suited to the flow-through modes.

FIG. 16 shows a flow-through lysing apparatus 1600 according to another illustrated embodiment. As described in more detail herein, the flow through lysis system 1600 may be operated in a flow-through stop or semi-batch mode, or in a continuous flow mode.

The flow-through lysing apparatus 1600 includes a container 1602 having a chamber 1604, and a micromotor 1606 coupled to drive an impeller 1608.

As illustrated, the chamber 1604 may have a first opening 1604 a that serves as an entrance providing fluid communication from an exterior 1610 of the container 1602 to the chamber 1604. Also as illustrated, the chamber 1604 may have a second opening 1604 b that serves as an exit, providing fluid communication from the chamber 1604 to the exterior 1610. The container 1602 may further have a third opening 1604 c sized to receive the impeller 1608 and to sealingly engage an outer portion of the micromotor 1606. Some embodiments may include a bushing or O-ring to form or enhance the sealing between the micromotor 1606 and third opening 1604 c.

A first coupler 1610 a may include a stem 1612 a sized to be sealingly received in the opening 1604 a to provide fluid communication into the chamber 1604. The stem 1612 a may be threaded with the hole 1604 a having a complementary thread. The first coupler 1610 a may include an attachment structure, for example, a ribbed nipple 1614 a to secure a tube 1616 a and provide a flow of material to be lysed to the chamber 1604. An O-ring 1618 a, or other similar structure, may enhance a seal between a flange of the first coupler 1610 a and the container 1602.

A second coupler 1610 b may include a stem 1612 b sized to be sealingly received in the opening 1604 b to provide fluid communication into the chamber 1604. The stem 1612 b may be threaded with the hole 1604 b having a complementary thread. The second coupler 1610 b may include an attachment structure, for example, a ribbed nipple 1614 b to secure a tube 1616 b and provide a flow of material to be lysed to the chamber 1604. An O-ring 1618 b, or other similar structure, may enhance a seal between a flange of the second coupler 1610 b and the container 1602.

Filters 1619 a, 1619 b may be positioned in the chamber to retain lysing particulate material therebetween. The filters 1619 a, 1619 b may, for example, take the form of nylon mesh filters with 50 micron openings mounted to suitable fittings.

The micromotor 1606 may, for example, take the form of a micromotor having a 4 mm diameter, and may be capable of driving the impeller at high speed, for example approximately 50,000 RPM, when not in the presence of liquid and beads. The impeller 1608 may be a nylon or acrylic impeller having a number of vanes. The vanes may be straight, without curvature or angle of attachment, such that movement of material is primarily circumferential. Should axial/horizontal movement of the material through the chamber be desirable, for example in a flow-through mode (e.g., FIGS. 16 and 17), such axial or flow movement comes from pumping and not from rotation of the impeller. This allows more precise control over amount of time that the material remains in the chamber and hence is subject to lysis. The vanes may, for example, produce a periodic flow at a frequency nearly 5 times as high as the embodiments of FIGS. 1A-4, however with a smaller amplitude of motion.

The lysing apparatus 1600 may also include a controller 1620 coupled to control the micromotor 1606. The controller 1620 may, for example include a motor controller and/or a programmed general purpose computing system, a special purpose computer, an application specific integrated circuit (ASIC) and/or field programmable gate array (FPGA). The controller 1620 may for example, be programmed or configured to cause the motor to pulsate. Pulsating may increase the effectiveness of the lysing.

FIG. 17 shows a flow-through lysing system 1700 according to one illustrated embodiment. As described in more detail herein, the flow-through lysis system 1700 may be operated in a flow-through stop or semi-batch mode, or in a continuous flow mode.

The flow-through lysing system 1700 includes a container 1702 having a chamber (not illustrated in FIG. 17), openings 1704 a, 1704 c (only two illustrated), and a micromotor 1706 coupled to an impeller (not shown in FIG. 17). The opening or entrance 1704 may be fluidly communicatively coupled to a pump 1720 that delivers material to be lysed from a reservoir 1722 via a first conduit or tube 1716 a. A second opening or exit may deliver lysed material to one or more downstream analysis apparatus 1724 via one or more conduits such as tubes 1716 b. As previously noted, downstream analysis may take a variety of forms, for instance nucleic acid amplification, electrophoresis, western blotting, mass spectrometry, gas chromatography, etc. The downstream analysis apparatus 1724 may be communicatively coupled to one or more computing systems 1726. The flow-through lysing system 1700 may also include one or more control systems 1728 which may control the micromotor 1706 and/or pump 1720. The control system 1728 may for example synchronize the pumping and oscillation, for example to implement a flow-through stop or semi-batch mode. The control system 1728 may for example control the pumping to attain a desired or defined residence time of the material in the chamber to achieve a desired or defined level of lysing, for example to implement a flow-through continuous mode.

The embodiments of FIGS. 16 and 17 may advantageously allow extremely high packing densities. In these embodiments, the volume of particulate material may advantageously exceed the volume of material to be lysed or may exceed the volume of material that has been lysed. Additionally or alternatively, these embodiments may advantageously have essentially no air in the chamber. As used herein, essentially no air means that the chamber is free of air other than small bubbles which may be unintentionally entrapped in the chamber. Such may increase lysing efficiency and prevent undesirable heating of the system from friction associated with liquid-air contact line motions.

FIG. 18 shows a lysing system 1800 according to another illustrated embodiment. The lysing system 1800 is particularly suitable for batch mode lysing operations.

The lysing system 1800 includes a container 1802 having a chamber 1804 that has a single opening 1804 a to provide fluid communication with an exterior of the container 1802. The apparatus 1800 includes a micromotor 1806 coupled to drive an impeller 1808 that is received in the chamber 1804. A portion of the micromotor 1806 is sized to form a sealing engagement with the container 1802 to seal the opening 1804 a. Some embodiments may include one or more bushings or O-rings (not shown) to ensure the seal.

Initially, the chamber 1804 is packed with material to be lysed 1810 and lysing particulate material 1812. After rotation of the impeller 1808, for a sufficient length of time, the chamber 1804 contains material that has been lysed and the lysing particulate material 1812. The micromotor 1806 and impeller 1808 may then be removed and the lysed material may be extracted, for example using a pipette 1814. The chamber 1804 of the batch mode embodiments may not be as densely packed as in flow-through embodiments since room may be required for the apparatus to withdraw the lysed material.

In some embodiments, off-the-shelf vials and tubes may be employed as the container 1802 to hold specimens of material to be lysed and the lysing particulate material, for example PCR or Eppendorf tubes.

The embodiment of FIG. 18 may advantageously allow extremely high packing densities. In these embodiments, the volume of particulate material may advantageously exceed the volume of material to be lysed or may exceed the volume of material that has been lysed. This embodiment is less likely to ensure that there is essentially no air in the chamber since room may be required for receiving the withdrawal apparatus (e.g., pipette). However, where possible, elimination of air in the chamber may increase lysing efficiency and prevent undesirable heating of the system from friction associated with liquid-air contact line motions.

FIG. 19 shows a method 1900 of operating a flow-through lysing apparatus and/or system according to one illustrated embodiment. Such may be useful in a flow-through stop or semi-batch mode or in a flow-through continuous mode.

At 1902, material to be lysed is received in the chamber of a container via an entrance. The chamber may already hold lysing particulate material. At 1904, the micromotor drives the impeller to cause the lysing particulate material to lyse the material to be lysed. At 1906, material that has been lysed is expelled from the chamber of the container via an exit.

FIG. 20 shows a method 2000 of evacuating material that has been lysed from a chamber, according to one illustrated embodiment.

At 2002, the material that has been lysed may be expelled via a first filter position before the exit in a flow path of material through the apparatus or system.

FIG. 21 shows a method 2100 of receiving material to be lysed in a chamber, according to another illustrated embodiment.

At 2102, the material to be lysed is received in the chamber via a second filter positioned following the entrance of the chamber in the flow path through the apparatus or system.

FIG. 22 shows a method 2200 of pumping material to be lysed into a chamber, according to another illustrated embodiment.

At 2202, the material to be lysed is intermittently pumped into the chamber via the entrance. Such may be particularly suitable for flow-through stop or semi-batch mode operation.

FIG. 23 shows a method 2300 of pumping material to be lysed into a chamber, according to one illustrated embodiment.

At 2302, the material to be lysed is continuously pumped into the chamber of the container via the entrance, at a flow rate that provides for a resident time of the material to be lysed in the chamber that is sufficiently long to achieve a desired or defined level of lysing. The micromotor may continuously drive the impeller to lyse the material. Such may be particularly suitable for flow-through continuous mode operation.

FIG. 24 shows a method 2400 of operating an impeller of a lysing system, according to one illustrated embodiment.

At 2402, the micromotor pulsatingly drives the impeller. Pulsations may be achieved by varying a voltage or current delivered to the micromotor. Pulsating may achieve a higher efficiency of lysing, thereby increasing throughput or decreasing time required to achieve a desired or defined level of lysing.

FIG. 25 shows a method 2500 of operating an impeller of a lysing system according to one illustrated embodiment.

At 2502, the micromotor drives the impeller at greater than 10,000 RPM in the presence of liquid and beads. Driving the impeller at a relatively high speed achieves a desired or defined level of lysing.

FIG. 26 shows a method 2600 of replacing a micromotor of a lysing system according to one illustrated embodiment.

At 2602, the micromotor may be replaced with a new micromotor. At 2604, the old micromotor may be disposed or recycled. This may be particularly useful since it is difficult to seal the internal elements (e.g., rotor, stator) of the high speed micromotor from exposure to the ambient environment, thus the micromotors may fail more frequently than in other embodiments or environments.

FIG. 27 shows a method 2700 of operating a batch based lysing apparatus according to one illustrated embodiment. The method 2700 may be particularly useful for use with the embodiment of FIG. 18.

At 2702, material to be lysed is received in a chamber of a first container via an entrance. The chamber may already hold a lysing particulate material or the lysing material may be provided into the chamber with or after the material to be lysed.

At 2704, an impeller is located in the chamber of the first container. At 2706, the entrance to the first container is closed or sealed with a micromotor. At 2708, the micromotor drives the impeller to circulate the material to be lysed and the lysing particulate material. The micromotor may drive the impeller for a sufficient length of time at a sufficient speed until a desired or defined level of lysing has occurred.

FIG. 28 shows a method 2800 of operating a lysing apparatus according to one illustrated embodiment. The method 2800 may be particularly useful for use with the embodiment of FIG. 18.

At 2802, the micromotor may be removed from the entrance of the first container. At 2804, the material that has been lysed is removed from the chamber of the first container via the entrance.

FIG. 29 shows a method 2900 of removing material that has been lysed according to one illustrated embodiment.

At 2902, the material that has been lysed may be withdrawn using a pipette.

FIG. 30 shows a method 3000 of operating a lysing apparatus according to another illustrated embodiment.

At 3002, the micromotor may be reused with one or more additional containers. It is noted that the micromotor, particularly when operated at high speed, may not be particularly well protected from the material to be lysed, lysing particulate material, or lysed material. Consequently, the micromotor may wear out. In many applications the micromotor may be employed to lyse multiple samples before failing.

FIG. 31 shows data on efficiency of lysis using an apparatus similar to that of FIG. 4.

A first curve 3102 represents measured fluorescence versus time of oscillation using an embodiment similar to that illustrated in FIG. 4. Fluorescence is proportional to the amount of nucleic acid released from cells. A second curve 3105 represents measured fluorescence versus time of oscillation using a commercially available “MINI-BEADBEATER-1 product from Biospec Products, Inc. of Bartlesville, Okla. As seen by comparison of the first curve 3102 and second curve 3105, the embodiment of FIG. 4 causes the release of cell contents more efficiently than the commercially available apparatus.

FIG. 32 illustrates a dependency of lysis efficiency on the frequency.

A curve 3202 appears to indicate a nearly quadratic dependence of the degree of lysis on frequency as controlled by changes to the applied voltage for a fixed amount of time.

FIG. 33 shows data representing spore lysis as a function of time for an embodiment similar to that illustrated in FIGS. 16 and 17.

The curves 3302, 3304 illustrate that the time to saturation is comparable to that of the embodiments of FIG. 4, but with peak efficiency of only 80%. The power required for this efficiency was only 400 mW, which is lower than the power used for various other embodiments.

FIG. 34A shows a bidirectional flow system 3400 for lysing, capturing, and eluting a biological material according to one illustrated embodiment. As described in more detail herein, the bidirectional flow system 3400 may be operated to lyse a biological specimen, to capture a biological material on a particulate material therein, and to elute the biological material therefrom. The system 3400 in FIG. 34A is particularly suited to lysing biological specimens and controlling direction and rate of flow, chemical compositions and physical characteristics of fluids within a lysing chamber to induce capture of biological materials by and elution of such materials from a particulate lysing material therein. Efficient use of system 3400 for lysis, capture and elution surprisingly may simply require control of flow direction, pH and salt concentration of fluids within the system. Under certain conditions, controlling temperature of certain of the fluids may also be advantageous.

In certain embodiments of the design of apparatus or systems herein, the design may include multiple modules, as further discussed below. Each module may be useful for carrying out particular aspects of the methods employing such apparatus or systems. Modules may be independently functional, but in a system may be joined, for example by snapping together or via Luer-Lock connectors.

In certain embodiments, the design of an integrated modular system for lysis of specimens and capture and elution of biological material of interest therefrom is such that multiple functions are carried out by the system. A system of such a design is particularly suitable for lysis, capture and elution of a biological material by control of fluid flow direction and chemical composition of the fluids within the system during different functions of the system or phases of operation. Functions of a system, such as that shown in FIG. 34A, exemplified by the specimen being cells and the biological material being DNA, may include the following: sample introduction; fluid movement; cell disruption and DNA capture; DNA elution; optionally heating and cooling; and optionally testing the isolated DNA. At least flow direction and chemical composition are controlled during each function.

In FIG. 34A, the bidirectional flow system 3400 for lysing, capturing and eluting a biological material includes a sample and elution module 3434, a lysing module 3410, a syringe 3413, and optionally a heater 3416. The sample and elution module 3434 includes a sample reservoir 3402 and an elution buffer reservoir 3420. The lysing module 3410 includes a lysing chamber 3412 and a micromotor 3430 coupled to an impeller 3431. During operation of the system 3400, the lysing chamber 3412 contains fluid and particulate lysing material. The particulate lysing material may be densely packed within the chamber. The syringe 3413 includes a barrel 3414 and a plunger 3415. The syringe 3413 may be operated manually or driven automatically, for example by positioning the syringe 3413 within a syringe pump (not shown in FIG. 34A). Syringe pumps are commercially available, for example from New Era Pump Systems, Inc. (Wantagh, N.Y., USA) The heater 3416 may be positioned to heat fluid within the barrel 3414 of the syringe 3413.

The sample reservoir 3402 of the sample and elution module 3434 is fluidly communicatively coupled via conduit 3404, valve 3406 and conduit 3408 to the lysing chamber 3412 of the lysing module 3410. In certain embodiments, the sample reservoir 3402 contains a biological specimen suspended or dissolved in a fluid having a chemical composition suitable to induce capture of a biological material by a particulate material in the lysing chamber 3412 upon release of the biological material from the biological specimen by lysis.

The elution buffer reservoir 3420 of the sample and elution module 3434 is fluidly communicatively coupled via conduit 3418, valve 3406 and conduit 3408 to the lysing chamber 3412 of the lysing module 3410. In certain embodiments, the elution buffer reservoir 3420 contains a fluid having a chemical composition suitable to induce release of biological material from particulate material on which it has been captured in the lysing chamber 3412.

The micromotor 3430 is electrically communicatively coupled to controller 3432. The controller may control the speed, duration and/or timing of operation of the micromotor, and thus the impeller 3431 within the lysing chamber 3412.

The lysing module 3410 is fluidly communicatively coupled to the barrel 3414 of the syringe 3413. The plunger 3415 of the syringe 3413 is positioned within the barrel 3414 of the syringe 3413. The plunger 3415 of syringe 3413 may be manually or controllably slidably operable to draw fluid into the barrel 3414 by moving the plunger 3415 in a direction so as to increase the volume within the barrel 3414. Alternatively, the plunger 3415 of the syringe 3413 may be manually or controllably slidably operable to force fluid out from the barrel 3414 by moving the plunger 3415 in a direction so as to decrease the volume within the barrel 3414. The barrel 3414 of the syringe 3413 is optionally in thermal contact with the heater 3416. The heater 3416 may, for example, include a band of an electrically resistive material, for instance a foil band. The heater 3416 may provide heat to the barrel 3414 of the syringe 3413 by closing a switch 3426 to supply voltage from a source 3428 to the heater 3416. The level of heat supplied to the barrel 3414 of the syringe 3413 may be controlled, for example via a potentiometer or some other controller (not shown in FIG. 34A).

The sample and elution module 3434 further includes an outlet tube 3422, fluidly communicatively coupled to the lysing chamber 3412 via conduit 3408 and valve 3406. The outlet tube 3422 is provided as a conduit to dispense eluted biological material into receptacle 3424 for further use, such as for testing or analysis. The plunger 3415 of the syringe 3413 may be operated manually or via a controller (not shown in FIG. 34A), for example controlling the operation of a pump, to draw fluid toward the barrel 3414 of the syringe 3413 at a first rate, to push fluid away from the barrel 3414 of the syringe 3413 at a second rate, and/or to stop flow for a period of time. The first rate and the second rate may be the same or different.

In a first phase of operation of system 3400, the plunger 3415 of the syringe 3413 may be operated to draw biological specimen from the sample reservoir 3402 via the valve 3406 into and/or through the lysing chamber 3412 into the barrel 3414 of the syringe 3413. In one embodiment thereof, the impeller 3431 may be operated while sample is drawn through the lysing chamber. In another embodiment, the impeller 3431 and/or the flow may be stopped intermittently. Further, the rate of flow or the rate at which the impeller 3431 is operated may be varied. Control of one or more of these variables may allow optimization of lysis of the biological specimen and/or collection of the biological material from the biological specimen.

A chemical composition of a fluid containing a biological specimen in the sample reservoir 3402 is selected to induce or permit capture of biological material from the biological specimen upon lysis of the biological specimen in the lysing chamber 3412. For example, in certain embodiments for isolation of nucleic acids, particularly DNA, from biological specimens, fluids in which the biological specimens may be suspended or dissolved within the sample reservoir 3402 in preparation for lysis and binding of the nucleic acid by particulate material in the lysing chamber 3412 may have high salt concentrations and/or low pH.

In embodiments of specimen-containing fluids with high salt concentrations, salt concentrations of such fluids in the sample reservoir 3402, suitable to induce binding of nucleic acid, particularly DNA, to the particulate material in the lysing chamber 3412, may vary from about 200 μM to about 500 μM. In other such embodiments, salt concentration of specimen-containing fluids suitable to induce binding of a nucleic acid, particularly DNA, may range up to about 1000 μM. In yet other such embodiments, salt concentration suitable to induce binding of nucleic acids, particularly DNA, may range up to about 2000 μM or greater.

In embodiments of specimen-containing fluids with low pH, pH of such fluids in the sample reservoir 3402, suitable to induce binding of nucleic acid, particularly DNA, to the particulate material in the lysing chamber 3412 may vary from about pH 3.5 to about pH 5. In other such embodiments, pH of the specimen-containing fluids to induce binding of a nucleic acid, particularly DNA, may vary from about pH 3.75 to about pH 4.25. In yet other such embodiments, pH of specimen-containing fluids to induce binding of nucleic acids, particularly DNA, may be about pH 4.

For example, the beads can be coated with antibodies specific to markers for pathogens, such as the enterotoxin B protein from Staphylococcus aureus. Similarly the beads can be coated with antibodies that bind markers for cancers, such as the p53 protein.

Also for example, in a “sandwich” approach, the beads can be pre-coated with a more universal receptor such as streptavidin therefore able to capture reagents that are conferred with the corresponding ligand such as biotin. Biotinylated antibodies are both readily available and easy to make. This approach allows one version of bead, such as streptavidin coated beads to serve as a generic product that can then be used to capture any specific protein by linking with the corresponding biotinylated antibody. The binding of the biotinylated antibody can be captured on the bead either as a manufacturing process prior to sample processing or by the user prior to processing a sample, or can be performed as part of the sample processing, combining beads, antibody and sample at the same time.

As a further example, an alternative “sandwich” approach to achieving a “universal” bead to capture specific protein is to pre-coat the bead with an antibody specific to antibodies of another species, such as mouse anti-goat IgG, then use goat antibody specific to the protein of interest.

In a second phase of operation of system 3400, the plunger 3415 of the syringe 3413 may be operated to push fluid out of the barrel 3414 of the syringe 3413 back through the lysing chamber to return specimen to the sample reservoir 3402 after capture or binding of the biological material therefrom. Nonspecific capture of DNA on the beads may occur during both the forward and the reverse passage of the sample through the lysing chamber. For sequence specific capture, the fluid in the barrel 3414 of the syringe 3413 may be heated and cooled before reversing the direction of flow, as further discussed below. The fluid in the sample reservoir at the end of the capture process is waste material or material that contains analytes of a different chemistry other than what is captured by the beads. So for example DNA may be captured on the beads and proteins that have not been exposed to denaturant can be returned to the sample chamber to then be analyzed for a specific protein. A quantity of air may be initially drawn into the barrel 3414 of the syringe 3413 at the beginning of the first phase of operation and used to force all of the waste fluid from the lysing chamber and the conduits into the sample/waste reservoir at the end of the first phase of operation.

In certain embodiments, the system may include particulate material having antibodies attached thereto to capture analyte protein or polypeptide markers while other particulate material remains dedicated to capturing nucleic acids. Further, labeled antibodies may be introduced during lysis and capture, for example, to label the protein or polypeptide. After capture, the labeled antibody may be eluted, for example with Urea. In a certain embodiment, for example, if a portion of the beads are designed for DNA capture and another portion for protein or polypeptide capture, capture of both may occur at the same time. In such an embodiment, the DNA may be elute with low salt and the protein or polypeptide with urea.

Beads that are design for captured of proteins can be manufactured separately from beads that are designed for capture of nucleic acid. After the separate manufacturing processes are complete then the two bead types can be combined in useful proportions into one cartridge that is then able to process proteins and nucleic acids. The beads that are designed for protein capture can be conferred with protein specific antibodies, or with protein specific aptamers, or with a universal receptor such as streptavidin, or with a binding agent that binds proteins that have been “engineered” for specific capture. This can include using Nickel coated bead used to capture proteins with Histidine tails.

Beads that are design for capture of nucleic acid can be generic, binding essentially all nucleic acids such as the silica or zirconium beads. Alternatively these beads can be conferred with specific nucleic acids (capture probes) that bind specific analytes by hybridization. Specific nucleic acid capture can also be facilitated by the sandwich approach by conferring the beads with a “universal” capture probe, and then providing a linker probe that has two domains, one domain complimentary to the analyte and the other domain complimentary to the “universal” capture probe.

Many combinations of beads for nucleic acids, specific or generic and be combined with beads for proteins, specific or generic with a single cartridge.

In a third phase of operation of system 3400, elution buffer may be drawn into the barrel 3414 of the syringe 3413 from the elution buffer reservoir 3420 via valve 3406 through lysing chamber 3412. As above, the flow may be continuous or intermittent and the rate and/or volume may be varied to optimize elution of biological material from the particulate lysing material. Further, the barrel 3414 of the syringe 3413 may be heated at this stage as well, for example to heat the elution fluid to optimize elution of captured biological material from the particulate material in the lysing chamber.

In certain embodiments of systems and methods for isolation of nucleic acids, particularly DNA, buffers for elution of the nucleic acids from the particulate material in the lysing chamber may have a lower salt concentration and/or a higher pH than the salt concentration and pH of the fluid in which the biological specimen containing the nucleic acids was suspended or dissolved to induce binding of the nucleic acids, particularly DNA, to the particulate material, as described above.

In embodiments of sample elution buffers with lower salt concentrations, the salt concentrations of the elution buffer placed in and drawn from the elution buffer reservoir 3420 may be less than about 200 μM. In other such embodiments, the salt concentrations of the elution buffers may be less than about 100 μM. In yet other such embodiments, the salt concentrations of the elution buffers may be less than about 10 μM. In particular such embodiments, the elution buffers may contain no salt.

In certain embodiments of sample elution buffers with higher pH, the pH of the elution buffers may be greater than about pH 5. In other such embodiments, the pH of the elution buffers may be greater than about pH 6. In yet other such embodiments, the pH of the elution buffer may be greater than about pH 7. In further such embodiments, the pH of the elution buffer may be greater than about pH 8.

In a fourth phase of operation, the eluted material may be pushed from the barrel 3414 of the syringe 3413 and the lysing chamber 3412 via conduit 3408, valve 3406 and outlet tube 3422 into receptacle 3424 for further manipulation or use, including analysis or testing. Air may again be expelled from the barrel 3414 of the syringe 3413 to force all of the fluid containing the biological material from the system and into the receptacle. Instead of collecting the eluate in a receptacle, the outlet tube may alternatively be connected directly to a testing apparatus in which the eluted material may be analyzed immediately upon elution. Outlet tubes may have narrow capillary sized channels to allow careful metering of the dispensed fluid, if necessary. The outlet may also include fluid sensing systems to monitor fluid flow and to provide feedback to the control system to control operation of the syringe 3413.

Use of a syringe 3413 to provide flow within the described lysis, capture and elution system provides an efficient contamination free approach, since the syringe 3413 can be readily and inexpensively replaced after each use of the system. While syringe pumps have been disclosed for use in the systems and methods disclosed herein, other types of pumps may be used, for example peristaltic pumps or other types of metering pumps. A particular advantage to use of syringe pumps or peristaltic pumps is that the syringe or tubing for the peristaltic pump is disposable and may be discarded along with the lysis chamber after each use. This provides a simple configuration for efficiently processing samples without concern for cross-contamination from one sample to the next. Although elimination of wash steps is a distinct advantage of the systems and methods disclosed herein, one or more wash steps could be included, if desired in particular embodiments, with wash fluid being provided via either the sample reservoir or the elution buffer reservoir.

Analysis or testing of biological materials obtained by systems and methods described herein may include, for example, subjecting DNA to amplification by PCR. In certain such procedures, the heater 3416 may be advantageously used. For example, in using the system 3434 to provide DNA for testing involving enzymatic amplification such as by PCR, the heater 3416 may supply heat to denature the DNA to form single strands in the barrel 3414 of the syringe 3413 prior to dispensing into the receptacle 3424. The heat-denatured DNA may then be cooled while still in the barrel 3414 of the syringe 3413 to prevent re-association of the strands. Such heat-denatured DNA may be particularly useful in enzymatic amplification reactions such as by PCR.

FIG. 34B shows positions of valve 3406 during certain phases of operation of system 3400 in FIG. 34A according to one illustrated embodiment.

Valve position 3406 a in FIG. 34B may be employed for two phases of operation. One phase corresponds to withdrawing biological specimen from sample reservoir 3402, via conduit 3404, valve 3406 and conduit 3408 into lysing chamber 3412 and barrel 3414 of syringe 3413. The other phase of operation using valve position 3406 a corresponds to pushing specimen remaining after lysis and collection from barrel 3414 of syringe 3413 and lysing chamber 3412 back into sample reservoir 3402 via conduit 3408, valve 3406 and conduit 3404.

Valve position 3406 b in FIG. 34B may be employed for a further phase of operation. This phase, an elution phase, corresponds to withdrawing elution buffer from elution reservoir 3420 via conduit 3418, valve 3406 and conduit 3408 into lysing chamber 3412 and barrel 3414 of syringe 3413.

Valve position 3406 c in FIG. 34B may be employed for yet another phase of operation. This phase, a dispensing phase, corresponds to pushing eluted biological material from barrel 3414 of syringe 3413 and lysing chamber 3412 into receptacle 3424 via conduit 3408, valve 3406 and outlet tube 3422.

Cellular samples for use in the systems disclosed herein, such as in FIG. 34A, may be obtained from a source such as a human or animal by use of swabs. Swabs may also be used to collect samples for testing from various surfaces that may hold cellular samples of interest. The cellular material collected on the swabs may then be suspended in fluid. Appropriate buffer, salts and mild detergent may be present in the fluid in order to drive the capture of DNA by the beads in the lysing chamber during lysis of the cells. The fluid sample containing the cells is placed, for example, in the sample reservoir in the sample and elution module of the system shown in FIG. 34A.

For example, binding of nucleic acid can be facilitated by cations provided by either sufficiently low pH, as low as 3.0 or sufficiently high enough concentration of salt such as NaCl, from 200 mM to 5 M, or Lithium Chloride, or ammonium Sulfate, or ammonium acetate. Chaotropic salts can be used up to 6 M.

High salt concentrations facilitate both non-specific binding of DNA to silica surfaces and sequence specific capture (hybridization) of DNA.

Detergents in the binding buffer may be used to reduce non-specific binding, such as Sodium Dodecyl Sulfate (SDS). If the detergent is compatible with nucleic amplification reactions such as PCR, then the need to wash away the detergent before elution of DNA can be avoided. These detergents are typically non-ionic and can include Tween, Triton, and Nonidet. If the salt that is used to facilitate binding the DNA is organic it may also serve to reduce non-specific binding, such as acetate as the anion or guanidinium as the cation.

Solutions that facilitate release and elution of DNA are low in ionic strength such as water, are typically buffered by concentration of buffer such as Tris at 10 mM to 30 mM. If the binding buffer has a low pH, such as pH 3 to 5 then it can help to neutralize it with a raised pH in the elution buffer, to include a range of pH 8 to 10. This will serve to facilitate release as well as compatibility with subsequent reactions of nucleic acid amplification.

Nucleic acids, in particular DNA, may be bound nonspecifically to the particulate lysing materials, as noted elsewhere herein. Alternatively, certain aspects of the materials and methods described herein may be adapted for sequence specific capture of nucleic acids. Sequence specific capture methods may be advantageous when nonspecific capture results in the capture of biological materials in addition to those of interest. For example, soil or stool samples may contain anionic polysaccharides that may be nonspecifically captured in addition to nucleic acids when using the systems and methods disclosed herein. In addition, stool samples may contain a variety of PCR inhibitors that may be nonspecifically bound and may then co-purify with nucleic acids, e.g., DNA. An alternative to using particulate materials that nonspecifically bind DNA and such other materials is to incorporate sequence specific capture probes on the particulate lysing materials. These probes would be selected on the basis of specificity for binding certain sequences in the nucleic acid(s) of interest. Such use of sequence specific capture would not only eliminate binding of non-nucleic acid materials, but would also eliminate binding of host nucleic acids from host cells gathered on the swabs. Sequence specific capture methods may thus increase sensitivity. The particulate materials or beads may be functionalized by a variety of methods for use in sequence specific capture.

For example, beads may be conferred with capture probes that bind the polymerase gene of HIV. The target specific sequence may range in length that facilitate sufficient affinity and specificity for the analyte, such as but not limited to 10 to 60 nucleotides long. The capture probes can further be designed with degeneracies, to facilitate capturing all or most variations of the analyte.

When using sequence specific capture, certain aspects of the methods for lysis, capture and elution, as described above, may vary. For example, in order to expose sequences in the DNA for specific binding by the probe, the double-stranded genomic DNA must be denatured to yield single-stranded DNA. This can be done by heat denaturation. Thus, when the specimen is passed through the lysing chamber and into the syringe, the syringe may then be heated to denature the DNA that has not already bound to the beads in the lysing chamber. The heating denatures the DNA to single-stranded DNA, which may then be cooled to inhibit re-annealing. In this manner the sequences of the heat denatured single-stranded DNA are exposed to allow specific binding to probe-containing beads during passage of the heated/cooled specimen back through the lysing chamber.

In certain embodiments, a system for lysing biological specimens and capturing and eluting biological material may be a lysing module having a lysing chamber containing particulate lysing material, e.g., beads, a micromotor-driven impeller and two syringes—a first syringe and a second syringe—each having a barrel fluidly communicatively coupled to the lysing chamber of the lysing module. The barrel of either one or both of the syringes may further have a heater in thermal contact therewith. Such a system may operate similarly to the system described above. For example, biological specimen may be pumped from a barrel of the first syringe into and through the lysing chamber into a barrel of the second syringe. The waste sample may then be pumped from the barrel of the second syringe back through the lysing chamber into the barrel of the first syringe or, if the first syringe has been removed, directly into a waste receptacle. A third syringe having a barrel containing elution buffer may then be substituted in place of the first syringe. The elution buffer may be delivered from the barrel of the third syringe through the lysing chamber into the barrel of the second syringe. The third syringe may then be either removed or replaced by a fourth syringe having a barrel. The elution buffer may then be pumped from the barrel of the second syringe back through and out of the lysing chamber and either into a receptacle or into the barrel of the fourth syringe. The barrel of the second syringe may be heated as described above, that is, during the lysis and capture phase and/or during the elution phase. Each syringe may simply be operated manually or may be operated automatically, for instance via a syringe pump, a motor and linkage, a solenoid, or other actuator.

During use of the systems described herein, the volume of sample passed through the lysing chamber for cell disruption and capture of biological materials, in particular DNA may be many times the volume of the lysing chamber. In certain embodiments, volumes of sample may range from 100 μL to 2000 μL. In certain particular embodiments of the systems and methods disclosed herein, the lysing module may be an OmniLyser™ (OL™) lysing apparatus. In particular embodiments using the OL™ lysing apparatus, processing samples of a volume noted above may take between about 15 and about 120 seconds.

The embodiment of the system and methods disclosed herein shown in FIGS. 34A and 34B and described in detail above exemplifies in a non-limiting manner isolating biological materials from biological specimens lysed using an impeller apparatus within the lysing chamber 3412. However, one of skill in the relevant art will recognize that the system exemplified in FIGS. 34A and 34B and its use could readily be adapted to isolation of biological materials that are released from biological specimens lysed by other means. For example, as described in detail elsewhere herein, such biological specimens may be lysed by oscillation of a lysing chamber. Further, lysing of specimens could be carried out ultrasonically, or could even include some other type of physical or chemical treatment, so far as the method of treatment yields a biological material having a chemical composition that is appropriate for binding of the biological material to particulate material within the lysing chamber and so far as the biological material captured by and eluted from the particulate material is suitable for further use or analysis.

FIGS. 35A and 35B show a lysing apparatus 3500, according to another illustrated embodiment.

The lysing apparatus 3500 includes a body 3502 that forms a chamber 3504. The body 3502 may have an opening 3506 sized and dimensioned to receive an impeller 3508 therethrough such that the impeller resides in the chamber 3504. The opening 3506 may optionally receive part or all of a drive motor, for instance a micro electric motor 3510. The electric motor 3510 is coupled to drive the impeller 3508. The electric motor 3510 is selectively operable in response to power supplied thereto. The electric motor 3510 may be secured in the opening 3506 via a press type fitting or interference fit. In particular, an inner wall forming the opening 3506 and/or chamber 3504 may be slightly tapered to sealing engage a side wall of the electric motor 3510 as the electric motor is advanced through the opening 3506 and into the chamber 3504. Alternatively, or additionally, a side wall of the electric motor 3510 may be slightly tapered to sealing engage a side wall of the opening 3506 and/or the chamber 3504 as the electric motor 3510 is advanced through the opening 3506 and into the chamber 3504. Alternatively, the electric motor 3510 and the opening 3506 and/or chamber 3504 may include coupler structures. For instance, the electric motor 3510 and the opening 3506 and/or chamber 3504 may include threads (not shown) which sealing mate together as the electric motor 3510 is advanced through the opening 3506 and into the chamber 3504. Alternatively, a bayonet (not shown) or lug type (not shown) coupler structure may be employed. Other sealing structures may be employed. For example, one or more gaskets, washers or O-rings (not shown) may be employed, with or without a seat or peripheral ring to seat the gasket, washers or O-rings. The seal may be a fluid tight seal and/or a gas tight seal.

The lysing apparatus includes a first port 3512 a and a second port 3512 b (collectively 3512). The first and second ports 3512 include passages 3514 a, 3514 b, respectively, (collectively 3514) to provide fluid communication with the chamber from an exterior thereof. The ports 3512 may be used to as input ports to supply material to the chamber 3504 and/or as output ports to remove material from the chamber 3504.

Each port 3512 may have a coupler 3516 a, 3516 b (collectively 3516) that allows selective coupling to the respective port 3512 a, 3512 b. For example, each of the ports 3512 may include a respective Luer-Lock® fitting or Luer-Slip® fitting, male or female. The Luer-Lock® or Luer-Taper® fittings allow the coupling of syringes 3518 a, 3518 b (FIG. 35A, collectively 3518) to the lysing apparatus 3500. For example, a first syringe 3518 a may be coupled to the first port 3512 a to allow sample or specimen injection, while a second syringe 3518 b may be coupled to the second port 3512 b to allow removal of a sample or specimen after lysing (i.e., lysed material). Such may allow the passage of a sample or specimen back and forth through the chamber 3504, for instance to enhance performance of the lysing or of DNA capture. Use of syringes 3518 may occur at either port 3512 a, 3512 b or at both ports 3512. The advantages of using a syringe 3518 as a sample or specimen delivery system include the fact that syringes 3518 are inexpensive, disposable, and employ positive displacement of fluid for a high degree of reliability in rapidly dispensing volumes. The Luer-Lock® design exemplifies a universal attachment that seals reliably and mates with many devices that also have complimentary Luer-Lock® fittings.

As illustrated in FIG. 36, selectively fastenable fittings, such as the Luer-Lock® fittings, may allow multiple lysing apparatus 3500 a-3500 b (collectively, 3500, only three illustrated) to be connected in succession. Such may advantageously be used to sequentially process a sample or specimen through multiple stages. Additionally, or alternatively, lysing particulate (e.g., beads) in the different sequential lysing apparatus 3500 may each have a respective receptivity for different molecules. For instance, the particulate in successive ones of the sequential lysing apparatus may be conferred with receptors (e.g., binding sites) to capture different respective molecules from the same sample or specimen. Each lysing apparatus 3500 with a different captured molecule, may then be easily separated from one another, and processed individually using different types of elution acts or steps.

FIGS. 37A and 37B show a lysing manifold or array 3700, according to one illustrated embodiment. The lysing manifold or array 3700 includes a block or frame 3702 that has a plurality of positions 3704 a, 3704 h (collectively 3704, only two called out in FIG. 37A) to hold respective ones of one or more individual lysing apparatus 3706 a-3706 h (collectively 3706, six illustrated). The individual lysing apparatus 3706 may, for example, take the form of distinct lysing apparatus which employ a chamber that receives an impeller and electric motor, for instance, the individual lysing apparatus 37006 may be identical or similar to the lysing apparatus 3500 (FIG. 35). Each individual lysing apparatus 3706 may include a respective disposable electric motor coupled to drive the impeller. Each individual lysing apparatus 3706 may include a first port 3708 a and a second port 3708 b (collectively 3708, only two called out in FIG. 37A). The ports 3708 may function as inlet and/or outlets to a chamber (not called out in FIGS. 37A or 37B).

As illustrated in FIG. 37B, the lysing manifold or array 3700 may include a support structure 3710 to support one or more blocks or frames 3702 and associated individual lysing apparatus 3706. In particular, the support structure 3710 may include rails 3710 a, 3710 b to hold the block or frame 3702 and associated individual lysing apparatus 3706 positioned relative to a structure that receives the lysed material, for example a plate such as a micro-titer plate 3712. For instance, the support structure 3710 may hold the block or frame 3702 such that the associated individual lysing apparatus 3706 are positioned above respective ones of a plurality of wells 3712 a (only one called out in FIG. 37B) of the micro-titer plate 3712. FIG. 37B shows only a single lysing manifold or array 3700 carrying a single row of individual lysing apparatus 3706, constituting a one-dimensional array of lying apparatus 3706. Alternatively, the support structure 3710 may carry additional lysing manifolds or arrays, each carrying a respective single row of individual lysing apparatus 3706. The individual lysing apparatus 3706 carried by the plurality of lysing manifolds or arrays 3700 can constitute a two-dimension array. As a further alternative, a single lysing manifold or array 3700 may carry individual lysing apparatus 3706 arranged in a two-dimensional array. As an even further alternatively, a motor and drive mechanism may be coupled to move a single lysing manifold or array 3700 carrying the individual lysing apparatus 3706 along the rails 3710 a, 3710 b of the support structure 3710. Thus, the one-dimensional array of lysing apparatus 3706 may be moved to address a two-dimensional array of positions. Movement may be controlled manually or automatically, for example via one or more computer processors, motors, actuators and or transmissions.

As described immediately above, individual lysing apparatus 3706 can be bundled together into a lysing manifold or array 3700 (e.g., one- or two dimensions) to facilitate multiplex processing. The distance between centers for these individual lysing apparatus 3706 can, for example, be 9 mm or a multiple of 9 mm to match a standard format of a micro-titer plate 3712 (e.g., with 9 mm spacing, 96 well plate or greater). Similarly, the use of electric motors with diameters below 4.5 mm allows the manifold or array of lysing apparatus 3700 to be used for micro-titer plate formats with 4.5 mm spacing (e.g., 384 well plate). Bundling the individual lysing apparatus 3706 in strips or rows of 4, 8, 6 or 12 may facilitate use for automated or semi-automated processing of samples in a micro-titer format. Additionally, if intake ports 3708 a of the individual lysing apparatus 3706 are designed to receive sample or specimen from pipette tips, then the individual lysing apparatus 3706 may be addressed by multichannel pipettors for either manual or robotic operation. The block or frame 3702 may be fabricated monolithically from a single block of material that has been molded or cut-extruded with multiple sites for the individual lysing apparatus 3706.

The flow through nature of some embodiments may allow for reuse of the system for processing additional samples or specimens. For example, the flow through nature may facilitate performance of one or more wash acts or steps to sterilize or otherwise sanitize or cleanse the system. Containers may be reused by cleaning and/or sterilizing the container between uses. This may be coordinated with downstream processing of one sample or specimen such that the container may be made ready for another sample or specimen during the downstream processing. One or more acts may be employed to clean and/or sterilize the container, for example using a high pH or low pH solution, bleach, detergent or combinations thereof. Adjusting pH may advantageously reduce the number of wash acts or steps, since the pH can be easily neutralized. An alternative approach may be the use of di-ethyl-pyrocarbonate (DEPC). DEPC compound can destroy proteins and nucleic acid. This treatment may be followed by a single wash and then a flow of hot air. Because DEPC is so volatile, it may be removed by degradation and evaporation during the act of passing heated air over any surfaces treated with the DEPC.

The various embodiments, whether flow through or not, may allow for analyte capture through various mechanisms either within the same chamber in which lysis occurs and/or in other chambers, for instance chambers arranged subsequently with respect to a flow of sample or specimen. As explained herein the flow through systems or apparatus (e.g., oscillating arcuate motion based or rotational impeller based) can be combined with analyte capture by using the same particulate matter (i.e., lysing particulate matter) used to perform lysis to capture analyte molecules within the same chamber. Additionally, or alternatively, lysis can also be combined with an act or step that uses another mechanism for analyte capture that may normally follow the lysis act. This approach still advantageously obviates the use of harsh reagents, as well as eliminating the associated need to perform wash acts or steps prior to any subsequent enzymatic reaction. For example, 1 μm magnetic particles can be combined with the sample or specimen before or after disruption (i.e., lysing). Thus, DNA capture can occur on these magnetic particles after the disruption has been accomplished by larger lysing particulate or beads. This principle may also be applied to other non-chemical approaches to cell lysis, such as sonication, where capture may occur on an additional surface at the same time or following sonication. Such may still allow wash acts or steps to be avoided before any enzymatic reaction.

Flow through configuration and high energy mixing of lysing particulate or beads may provide distinct advantages in binding and elution kinetics. By passing the sample or specimen through a relatively small chamber with a dense suspension of lysing particulate or beads that are actively shaken up or stirred, induces a high rate of “collisions” between analyte DNA and the lysing particulate or beads. This may be similar is some respects to passing a sample or specimen through an affinity filter, providing a stark advantage over the common approach of using micron-sized magnetic beads. Such magnetic beads typically must be dispersed throughout the entire sample or specimen volume.

The interface between a solid phase and a solution phase has a boundary layer in the liquid phase that is relatively static and does not participate in active mixing. The molecules in the solution phase must diffuse through this layer to reach the surface of the solid phase. Diffusion is a slow process compared to turbulent mixing and convection. As the energy of motion of the lysing particulate or beads increases, the extent of active mixing increases, reducing this boundary layer and serving to increase the rate of arrival of DNA toward the bead surface, thus accelerating the binding. Alternatively, when eluting the DNA, the high energy motion of the lysing particulate or beads can also accelerate the dissociation of the DNA from the lysing particulate or beads by serving to escort the DNA away from the lysing particulate or beads and the boundary layer. This can be especially helpful in the common case where the DNA binding system has a large binding capacity to capture a large load DNA, e.g., 5 to 60 μg, but is also useful in capturing very low loads of analyte DNA. The high binding capacity will normally reduce the efficiency of elution for low copy numbers by offering so much surface area to re-bind with and so much boundary layer that can retain some of the DNA. The shear forces generated by the high energy motion generated by the oscillating arcuate motion based embodiments (FIGS. 1A-5) or the rotational impeller based embodiments (FIGS. 16-18) can contribute to dissociating DNA from the surface and to escorting DNA from the reduced boundary layer, enabling the DNA to join the bulk fluid that is dispensed out of the chamber during the elution act or step.

At least some of the embodiments described herein may enable a “sandwich” type of detection scheme using the lysing particulate or beads. This principle can apply to proteins and to nucleic acids, as well as other ligand/receptor combinations. In the case of nucleic acids, a DNA capture scheme such as a branched DNA assay developed at Chiron can be performed on the lysing particulate (e.g., beads) used to lyse cells and bind DNA in either the oscillating arcuate motion based apparatus (i.e., bead beater) or the rotational impeller based apparatus (i.e., bead blender). Analyte nucleic acid can be captured by heterobifunctional extender probes that can crosslink analyte sequence to capture probes that are attached to the lysing particulate or beads. Subsequent layers of branched DNA assay can be added to the captured analytes on the lysing particulate or beads. Each layer of probe can be accompanied with an adjusted speed of lysing particulate or bead mixing to mediate between the acceleration of binding of each layer and the DNA scission that is associated with the high shear forces. Building the branched DNA scheme on these lysing particulate or beads can facilitate rapid binding kinetics for each layer of binding including the capture of analyte. This can also facilitate very efficient concentration of analyte from very large volumes and can facilitate efficient wash acts or steps between binding acts or steps.

After an entire complex of probes of the branched DNA scheme has been built on the lysing particulate or beads, there are at least three ways to proceed to detection. One is to detect within the container or cartridge of the lysing apparatus (e.g., bead blender). In the case of chemiluminescent detection, mixing can occur during the detection act or step. Another approach is to dispense the lysing particulate or beads into a well or tube for detection. A further approach is to release the DNA complex from the lysing particulate or beads and elute the reporter groups into a well or tube for detection. This approach has the potential advantage of providing a better ratio of analyte specific signal to background signal by enabling a release act or step that is in fact analyte specific. For example, one or more layer of probes may be released by cleaving with light at photo-cleavable junctions. Eluting in high pH, or in low salt with heat can denature the DNA and thereby release the reporter group. Nucleases may be used to release the DNA complex at specific sites or non-specifically. The rapid movement provided by the oscillating rotational motion based apparatus (i.e., bead beater) or the rotational impeller based apparatus (i.e., bead blender) may enhance the efficiency of the release or elution act or step.

As will be recognized by those of ordinary skill in the art based on the teachings herein, the use of lysing particulate or beads to lyse cells and to extract DNA can be performed using any surface chemistry that has a nonspecific affinity for DNA. This can include using silica or silica like beads and employing high salt or low pH to induce DNA to bind to beads followed by application of a low salt solution to elute the DNA according to the Boom method. The can also include using negatively charged beads that when accompanied by a solution of divalent cations such as Mg++, will form a salt bridge between the beads and DNA. This approach also uses low salt and EDTA to elute the DNA. Such is described at Hawkins, of al., Nucleic Acids Res. 1995, 23:22. This may also include capturing and releasing DNA with anion exchange resins on silica lysing particulate or beads. A resin such as diethylaminoethanol that contains a tertiary amine can bind DNA in low pH and can then elute DNA in the presence of a medium to high salt concentration.

FIGS. 38A and 38B show a lysis apparatus in the form of a stopcock valve 3800, according to yet another illustrated embodiment. The stopcock valve 3800 includes an outer body portion 3802 that forms a receptacle or outer chamber 3804. The stopcock valve 3800 includes an inner body portion 3806 that forms a receptacle or inner chamber 3808. The stopcock valve 3800 also includes an impeller 3810 received in the inner chamber 3808 for rotation therein. The stopcock valve 3800 further includes an electric motor 3812 coupled to drive the impeller. The stopcock valve 3800 may additionally include a handle 3818 or other engageable structure to allow a torque to be applied to the inner body portion 3806 to allow such to be easily rotated or pivoted with respect to the outer body portion 3802.

The inner body portion 3806 is rotatable (double headed arrow 3807) in the inner chamber 3808 about a longitudinal axis 3809 to open and close a plurality of ports 3820 a-3820 c (collectively 3820), thereby providing or shutting off fluid communication with the inner chamber 3808. Such may be employed to allow the passage of different fluids through the inner chamber 3808 at different times during the operation of the stopcock valve lysis apparatus 3800 and/or for defining different flow paths through the stopcock valve lysis apparatus 3800. The structure may ensure that one or more ports in the wall of the inner chamber 3808 fluidly communicate with a port, channel or passage through the outer body portion 3802. Thus, a port 3820 may be aligned with a channel to a pump, while at least one other port 3820 in the fluidly communicates with a channel containing a fluid intended to pass through the inner chamber 3808. This design enables the stopcock lysis apparatus 3800 to integrate with other chambers that serve other functions or which hold other fluids, such as a mix of the sample and binding buffer, elution buffer, pump, a waste reservoir, and/or chamber for amplification and detection.

FIGS. 39A-39C show a lysis apparatus 3900, similar to that of FIGS. 38A and 38B. In particular, FIG. 39A is an exploded view of the lysis apparatus 3900, FIG. 39B is assembled view, and FIG. 39C shows a portion of the lysis apparatus 3900 rotated 180 degrees from an orientation illustrated in FIG. 39A.

The lysis apparatus 3900 may include an outer vessel 3902 that forms an outer chamber 3904, an inner vessel 3906 that forms an inner chamber 3908, an impeller 3910 and an electric motor 3912 coupled to drive the impeller 3910. The outer chamber 3904 is sized to receive the inner vessel 3906 therein. For example, the outer chamber 3904 may have an inner peripheral or inner diameter D₁ that closely receives an outer periphery or outer diameter D₂ of the inner vessel 3906. Such may be sufficiently closely received as to form a fluid tight or a gas tight seal therebetween. Additionally, or alternatively, one or more gaskets, washers or O-rings may be employed. Additionally, or alternatively, a coupler structure (e.g., threads) may be employed. The outer chamber 3904 is open at one end 3914 a, to receive the inner vessel 3906. The outer chamber 3904 may be closed at the opposite end 3914 b. The inner chamber 3908 is open at one end 3916 a, to receive the impeller 3910 and, optionally electric motor 3912. The inner chamber 3908 may be open at the opposite end 3916 b (as illustrated in FIGS. 39A and 39C), for example where the outer chamber 3904 is closed at the opposite end 3914 b. Alternatively, the inner chamber 3908 may be closed at the opposite end 3916 b (as illustrated in FIGS. 40A and 40B).

The inner chamber 3908 is sized to receive the impeller 3910, and optionally part or all of the electric motor 3912 therein. For example, the inner chamber 3908 may have an inner peripheral or inner diameter D₃ that closely receives an outer periphery or outer diameter D₄ of the electric motor 3912. Such may be sufficiently closely received as to form a fluid tight or a gas tight seal therebetween. Additionally, or alternatively, one or more gaskets, washers or O-rings may be employed. Additionally, or alternatively, a coupler structure (e.g., threads) may be employed. The inner vessel 3902 may include one or more protrusions or other engageable structure 3918 a, 3918 b (collectively 3918) extending outwardly therefrom. Such allows the inner vessel 3906 to be easily rotated within the outer vessel 3902.

As best illustrated in FIG. 39A, the outer vessel 3902 has a number of ports 3920 a-3920 c (collectively 3920) to provide fluid communications or a fluid path between the outer chamber 3904 and an exterior of the outer vessel 3902. Three ports 3920 a-3920 c are shown in the illustrated embodiment, although fewer or greater number of ports may be employed. Likewise, the inner vessel 3906 has a number of ports 3922 a-3922 c (collectively 3922) to provide fluid communications or a fluid path between the inner chamber 3908 and an exterior of the inner vessel 3906. Three ports 3922 a-3922 c are shown in the illustrated embodiment, although fewer or greater number of ports may be employed. The ports 3920, 3922 arranged such that selected ports on the inner vessel 3906 align with selected ports on the outer vessel 3902 in a first orientation or configuration (FIG. 39A), while selected ports on the inner vessel 3906 align with selected ports on the outer vessel 3902 in a second orientation or configuration (FIG. 39C), different from the first orientation or configuration. The fluid path can be modified by simply orienting the inner vessel 3906 with respect to the outer vessel 3902. For example, in the illustrated embodiment, a first fluid path between ports 3920 a, 3920 b of the outer vessel 3902 is established when the inner vessel 3906 is in a first orientation (FIG. 39A) with respect to the outer vessel 3902. Rotating the inner vessel 3906 with respect to the outer vessel 3902, for instance 180 degrees about a longitudinal axis (orientation illustrated in FIG. 39C), establishes a second fluid path between ports 3920 a, 3920 c of the outer vessel 3902. Notably, the inner wall or periphery that forms the outer chamber 3904 selectively seals one of the ports 3922 a, 3922 c of the inner vessel 3906 depending on the orientation of the inner vessel 3906 with respect to the outer vessel 3902. Other embodiments may employ additional ports. Ports may be oriented at angles other than 180 degrees from one another. Thus, for example, the inner vessel 3906 may have ports oriented at 90 degrees, 60 degrees or 45 degrees from each other. Such may provide a greater number of selectively selectable fluid paths. While the outer and inner vessels 3902, 3906, respectively, are illustrated having an equal number of ports 3920, 3922, respectively, in some embodiments the number of ports of the outer and inner vessels 3902, 3906 may not be equal to one another.

FIGS. 40A and 40B show a show a lysis apparatus 4000, similar to that of FIGS. 38A and 38B. In particular, FIG. 40A is an exploded view of the lysis apparatus 4000 and FIG. 40B shows a bottom of the lysis apparatus 4000.

The lysis apparatus 4000 may include an outer vessel 4002 that forms an outer chamber 4004, an inner vessel 4006 that forms an inner chamber 4008, an impeller 4010 and an electric motor 4012 coupled to drive the impeller 4010. The outer chamber 4004 is sized to receive the inner vessel 4006 therein. For example, the outer chamber 4004 may have an inner peripheral or inner diameter that closely receives an outer periphery or outer diameter of the inner vessel 4006. Such may be sufficiently closely received as to form a fluid tight or a gas tight seal therebetween. Additionally, or alternatively, one or more gaskets, washers or O-rings may be employed. Additionally, or alternatively, a coupler structure (e.g., threads) may be employed. The outer chamber 4004 may be open at both ends 4014 a, 4014 b, to receive the inner vessel 4006. The inner chamber 4008 is open at one end 4016 a to receive the impeller 4010 and, optionally electric motor 4012. The inner chamber 4008 is closed at the opposite end 4016 b which thus closes the opposite end 4014 b of the outer chamber 4004. The inner vessel 4006 has one or more protrusions or other engageable structure 4018 extending from the opposite end 4016 b thereof. Such allows the inner vessel 4006 to be easily rotated within the outer vessel 4002.

The inner chamber 4008 is sized to receive the impeller 4010, and optionally part or all of the electric motor 4012 therein. For example, the inner chamber 4008 may have an inner peripheral or inner diameter that closely receives an outer periphery or outer diameter of the electric motor 4012. Such may be sufficiently closely received as to form a fluid tight or a gas tight seal therebetween. Additionally, or alternatively, one or more gaskets, washers or O-rings may be employed. Additionally, or alternatively, a coupler structure (e.g., threads) may be employed.

As best illustrated in FIG. 40A, the outer vessel 4002 has a number of ports 4020 a-4020 c (collectively 4020) to provide fluid communications or a fluid path between the outer chamber 4004 and an exterior of the outer vessel 4002. Three ports 4020 a-4020 c are shown in the illustrated embodiment, although fewer or greater number of ports may be employed. Likewise, the inner vessel 4006 has a number of ports 4022 a-4022 c (collectively 4022) to provide fluid communications or a fluid path between the inner chamber 4008 and an exterior of the inner vessel 4006. Three ports 4022 a-4022 c are shown in the illustrated embodiment, although fewer or greater number of ports may be employed. The ports 4020, 4022 arranged such that selected ports on the inner vessel 4006 align with selected ports on the outer vessel 4002 in a first orientation or configuration (FIG. 40A), while selected ports on the inner vessel 4006 align with selected ports on the outer vessel 4002 in a second orientation or configuration, different from the first orientation or configuration. The fluid path can be modified by simply orienting the inner vessel 4006 with respect to the outer vessel 4002. For example, in the illustrated embodiment, a first fluid path between ports 4020 a, 4020 b of the outer vessel 4002 is established when the inner vessel 4006 is in a first orientation (FIG. 40A) with respect to the outer vessel 4002. Rotating the inner vessel 4006 with respect to the outer vessel 4002, for instance 180 degrees about a longitudinal axis, establishes a second fluid path between ports 4020 a, 4020 c of the outer vessel 4002. Notably, the inner wall or periphery that forms the outer chamber 4004 selectively seals one of the ports 4022 a, 4022 c of the inner vessel 4006 depending on the orientation of the inner vessel 4006 with respect to the outer vessel 4002. Other embodiments may employ additional ports. Ports may be oriented at angles other than 180 degrees from one another. Thus, for example, the inner vessel 4006 may have ports oriented at 90 degrees, 60 degrees or 45 degrees from each other. Such may provide a greater number of selectively selectable fluid paths. While the outer and inner vessels 4002, 4006, respectively, are illustrated having an equal number of ports 4020, 4022, respectively, in some embodiments the number of ports of the outer and inner vessels 4002, 4006 may not be equal to one another.

While the embodiments of FIGS. 38A-38B, 39A-39C, 40A-40B may all be manually operated (e.g., manually rotated to select a desired flow path or port), some embodiments may be automatically operated, for example drive by an electric motor, solenoid or other electrical or electromechanical actuator.

The lysis and DNA extraction systems can be integrated with other components and functions. This is especially true of pumps and valves that further enable integration of waste reservoirs, wash reservoirs and functions, chambers for sample or specimen introduction, elution buffer chambers and functions, chambers and functions for amplification and detection. All of these structures and functions can be integrated into a disposable container or cartridge that includes the bead beating function for either lysis or analyte extraction or both. Integrating these structures and functions into a disposable unit has practical advantages for point-of-care and point-of-use diagnostic applications. Integrating these structures functions into a disposable unit has practical advantages for point-of-care and point-of-use diagnostic applications.

The various embodiments described above can be combined to provide further embodiments. U.S. provisional patent application Ser. No. 61/020,072 filed Jan. 9, 2008; International Patent Application Serial No. PCT/US2009/030622 filed Jan. 9, 2009 and published as WO2009/089466; U.S. provisional patent application Ser. No. 61/117,012 filed Nov. 21, 2008; U.S. provisional patent application Ser. No. 61/220,984 filed Jun. 26, 2009 U.S. nonprovisional patent application Ser. No. 12/732,070 filed Mar. 25, 2010; filed U.S. provisional patent application Ser. No. 61/317,604 filed Mar. 25, 2010; and U.S. nonprovisional patent application Ser. No. 12/823,081 are incorporated herein by reference, in their entirety. Aspects of the embodiments can be modified, if necessary to employ concepts of the various patents, applications and publications to provide yet further embodiments.

These and other changes can be made to the embodiments in light of the above-detailed description. In general, in the following claims, the terms used should not be construed to limit the claims to the specific embodiments disclosed in the specification and the claims, but should be construed to include all possible embodiments along with the full scope of equivalents to which such claims are entitled. Accordingly, the claims are not limited by the disclosure. 

1-45. (canceled)
 46. A device to lyse cell specimens which include cells containing a biological material including at least one of nucleic acids or proteins or polypeptides, the device comprising: an outer vessel that forms an outer chamber therein having a circular cross-section with an inner diameter D1, the outer vessel having at least two outer vessel ports to provide respective fluid communicative paths between the outer chamber and an exterior of the outer vessel; an inner vessel that forms an inner chamber therein, the inner vessel having a circular cross-section with an outer diameter D2 sized to be closely and pivotably received in the outer chamber of the outer vessel with a fluid tight seal therebetween, the inner vessel having two or more inner vessel ports to provide fluid communicative paths between the inner chamber and an exterior of the inner vessel, the inner vessel ports positioned such that at a first rotational orientation of the inner vessel relative to the outer vessel, at least one of the inner vessel ports is aligned with one of the outer vessel ports and at a second rotational orientation of the inner vessel relative to the outer vessel, at least one inner vessel port is aligned with a different one of the outer vessel ports, wherein when aligned the inner vessel ports and the outer vessel ports provide a fluid communicative path between the exterior of the outer vessel and the inner chamber of the inner vessel; an impeller sized to be received in the inner chamber of the inner vessel; and a motor drivingly coupled to drive the impeller.
 47. The device of claim 46 wherein in use the motor closes the inner chamber of the inner vessel from an exterior of the device.
 48. The device of claim 46 wherein the inner chamber of the inner vessel has an inner diameter D3 and the motor has an outer diameter D4, at least a portion of the motor closely received by the inner chamber to provide a fluid tight seal therebetween.
 49. The device of claim 48, further comprising: at least one of a ring, a gasket or a washer which provides a fluid tight seal between the inner and the outer vessels or between the motor and the inner vessel.
 50. The device of claim 46, further comprising: at least one filter having a plurality of openings sized to block particulate lysing material.
 51. The device of claim 46, further comprising: a medium including a fluid and a particulate lysing material comprising a plurality of beads contained in the inner chamber of the inner vessel.
 52. The device of claim 51 wherein particulate lysing material has a binding affinity for the biological material in the presence of the fluid and the fluid has a physical characteristic that induces binding of the biological material to the particulate lysing material, the binding affinity sufficient to bind at least some of the biological material to at least some of the particulate lysing material in the presence of the fluid.
 53. The device of claim 51 wherein the particulate lysing material includes at least one of a plurality ceramic beads, a plurality of glass beads, a plurality of zirconium beads, a plurality of silica beads, a plurality of sand, or a plurality of beads with a metal core coated by latex.
 54. The device of claim 51 wherein the particulate lysing material has diameters or smallest lateral dimensions in a range of 10 microns to 600 microns.
 55. The device of claim 51 wherein the fluid has a high salt concentration of at least 500 millimolar.
 56. The device of claim 51 wherein the fluid has a high salt concentration of at least 200 millimolar.
 57. The device of claim 51 wherein the fluid has a pH from pH 3.5 to pH
 5. 58. The device of claim 57 wherein the pH is no lower than
 4. 59. A method to lyse cell specimens which include cells containing a biological material including at least one of nucleic acids or proteins or polypeptides using a device, the method comprising: introducing the cell specimen to the device, the device comprising: an outer vessel that forms an outer chamber therein having a circular cross-section with an inner diameter D1, the outer vessel having at least two outer vessel ports to provide respective fluid communicative paths between the outer chamber and an exterior of the outer vessel; an inner vessel that forms an inner chamber therein which holds a particulate lysing material, the inner vessel having a circular cross-section with an outer diameter D2 sized to be closely and pivotably received in the outer chamber of the outer vessel with a fluid tight seal therebetween, the inner vessel having two or more inner vessel ports to provide fluid communicative paths between the inner chamber and an exterior of the inner vessel, the inner vessel ports positioned such that at a first rotational orientation of the inner vessel relative to the outer vessel, at least one of the inner vessel ports is aligned with one of the outer vessel ports and at a second rotational orientation of the inner vessel relative to the outer vessel, at least one inner vessel port is aligned with a different one of the outer vessel ports, wherein when aligned the inner vessel ports and the outer vessel ports provide a fluid communicative path between the exterior of the outer vessel and the inner chamber of the inner vessel; an impeller sized to be received in the inner chamber of the inner vessel; and a motor drivingly coupled to drive the impeller; operating the motor to lyse the cell specimen; rotating the inner vessel from a first rotational orientation to a second rotational orientation in which a one of the inner vessel ports aligns with a one of the outer vessel ports to provide a fluid communicative path between the inner chamber of the inner vessel and the exterior of the outer vessel; and removing the biological material from the inner chamber of the inner vessel.
 60. The method of claim 59, further comprising: before introducing the cell specimen to the device, rotating the inner vessel to the first rotational orientation to align one of the inner vessel ports with a different one of the outer vessel ports than in the second rotational orientation.
 61. The method of claim 59, further comprising: introducing a fluid into the inner chamber of the inner vessel.
 62. The method of claim 61 wherein introducing a fluid into the inner chamber of the inner vessel includes introducing a fluid in which the particulate lysing material has a binding affinity for the biological material in the presence of the fluid and the fluid has a physical characteristic that induces binding of the biological material to the particulate lysing material, the binding affinity sufficient to bind at least some of the biological material to at least some of the particulate lysing material in the presence of the fluid.
 63. The method of claim 61 wherein introducing a fluid into the inner chamber of the inner vessel includes introducing the fluid into the particulate lysing material which includes at least one of a plurality of ceramic beads, a plurality of glass beads, a plurality of zirconium beads, a plurality of silica beads, a plurality of sand, or a plurality of beads with a metal core coated by latex.
 64. The method of claim 61 wherein introducing a fluid into the inner chamber of the inner vessel includes introducing the fluid into the particulate lysing material which has diameters or smallest lateral dimensions in a range of 10 microns to 600 microns.
 65. The method of claim 61 wherein introducing a fluid into the inner chamber of the inner vessel includes introducing the fluid having a high salt concentration of at least 500 millimolar.
 66. The method of claim 61 wherein introducing a fluid into the inner chamber of the inner vessel includes introducing the fluid having a high salt concentration of at least 200 millimolar.
 67. The method of claim 61 wherein introducing a fluid into the inner chamber of the inner vessel includes introducing the fluid having a pH from pH 3.5 to pH
 5. 68. The method of claim 61 wherein introducing a fluid into the inner chamber of the inner vessel includes introducing the fluid having a pH no lower than
 4. 69. The method of claim 59, further comprising: flowing a volume of the cell specimen through the inner chamber that exceeds a volume of the inner chamber.
 70. The method of claim 59, further comprising: flowing the cell specimen through the inner chamber in a first direction at a first time and at a first rate, and in a second direction, opposite the first direction, at a second time and at a second rate.
 71. The method of claim 59, further comprising: before introducing a cell specimen to the device, placing the motor at least partially into the inner chamber of the inner vessel to seal the inner chamber from an exterior of the device. 